Fitness testing scale

ABSTRACT

Fitness testing scale systems and methods are implemented using a variety of approaches. According to one implementation, a fitness testing scale measures the physiological data of a user engaging sensor circuitry on a platform region of the scale. In a fitness testing mode, physiological data of the user is detected at respective states of physical exertion. The physiological data is then processed by user-targeted circuitry to determine physiological parameters of the user pertaining to the respective physical exertion states, such as may pertain to an increase in exertion or a reduction in exertion. These physiological parameters may, for example, be used to provide an indication of the physical health and fitness of the user. Such parameters may then be associated with the user and saved to a data-access circuit, and also forwarded to a display which communicates the physiological parameters among other information to the user through the platform region.

Various aspects of the present disclosure are directed toward auser-support platform that can include and/or be implemented as alarge-area display user-weighing scale and multisensory biometricweighing scale devices, systems, and methods for testing and/orencouraging the physical fitness of a user. Such embodiments may, forexample, involve interacting with a user at one or more exertionconditions, and therefrom obtaining physiological characteristics of theuser. These characteristics are provided or otherwise used to ascertainone or more fitness conditions associated with the user. For instance,by obtaining or using baseline type characteristics pertaining to anon-exertion or resting state (e.g., at resting heart rate),physiological characteristics that are later obtained from the userwhile the user's heart rate is elevated (at a state of exertion) can beused with the baseline type characteristics to generally characterizethe user's fitness.

One specific aspect of the present disclosure relate to a weighing scaleincluding a platform region for supporting a user while the user standson the platform region, user-targeted circuitry, a display configuredand arranged with the support structure for displaying data through theplatform region, and a base unit configured and arranged to integrate asupport structure including the platform region and sensor circuitrytherein. The platform region is configured to engage the user with thesensor circuitry while the user stands on the platform region and tocollect physiological data from the user via the sensor circuitry. Thedisplay and the user-targeted circuitry are configured to operate in afitness testing mode by instructing a user to engage the sensorcircuitry via the platform region for measuring parameters of the userrelative to baseline user measurements, to cause change to the user'sheart rate by increasing or decreasing physical exertion, andthereafter, upon recognizing that the user has returned to the supportstructure, to engage the sensor circuitry via the platform region andcollect and collate user physiological data.

Additional aspects of the present disclosure relate to electronic bodyplatforms and/or scales that weigh the user and/or provideimpedance-based biometric measurements, as may be implemented withfitness-based approaches as discussed above or otherwise herein.

Biometrics is a broad term wherein this application includes themeasurements of body composition and cardiovascular information.Impedance measurements can be made through the feet to measure fatpercentage, muscle mass percentage, and body water percentage.Additionally, foot-impedance-based cardiovascular measurements can bemade for an electrocardiogram (ECG) and sensing the properties of bloodpulsations in the arteries, also known as impedance plethysmography(IPG), where both techniques can be used to quantify heart rate and/orpulse arrival timings (PAT). Cardiovascular IPG measures the change inimpedance through the corresponding arteries between the sensingelectrode pair segments synchronous to each heartbeat. One or more ofthese aspects may be implemented to provide fitness-basedcharacterizations.

In some embodiments of the present disclosure, a weighing scale isdisclosed that includes a base unit which integrates a supportstructure, a display, user-targeted circuitry, and a communicationdriver, and operates for providing fitness-based characterization viathe user-targeted circuitry. The support structure has a platform regionwith sensor circuitry and which engages a user via the sensor circuitrywhile the user stands on the platform region. The sensor circuitrycollects physiological data from the user such as measurements of bodycomposition and cardiovascular information which are then forwarded onto the user-targeted circuitry for analysis. The display displays datathrough and throughout the entire platform region, includingentertainment information, and physiological parameters of the user asdetermined by the user targeted circuitry.

The user-targeted circuitry operates in a fitness testing mode byinstructing a user to engage the sensor circuitry on the platform regionof the weighing scale, during a reduced-exertion state of the user,thereby allowing the sensor circuitry to collect physiological data fromthe user. The user-targeted circuitry also instructs the user to raisehis or her exertion level by exercising, and to again engage the sensorcircuitry on the platform region of the weighing scale, immediatelyafter physical exertion. The respectively-collected sets ofphysiological data may be collected in any order, such as by firstcollecting data in a reduced-exertion or resting state and latercollecting data in an exerted state, or by first collecting data in anexerted state and later collecting data at a predetermined time aftercollecting the data in the exerted state.

The sensor circuitry thus collects physiological data from the userindicative of a physical exertion state of the user under differentconditions. The user-targeted circuitry receives the physiological datafrom the sensor circuitry (including both the physiological dataindicative of the reduced-exertion state and a higher exertion state),and determines physiological parameters of the user based on thephysiological data and the associated physical state. The communicationdriver receives the information (including the determined physiologicalparameters) from the user-targeted circuitry and provides theinformation to the display for viewing by the user through the platformregion. Accordingly, the displayed physiological data can provide theuser with indications as to their level of physical fitness orindication of a physiological condition.

In some embodiments, the weighing scale also includes a data-accesscircuit that provides access to user-specific data. Such user-specificdata may include, for example, physiological parameters of the user thatare stored in response to or developed by the user-targeted circuitry.

Various example embodiments may be more completely understood inconsideration of the following detailed description in connection withthe accompanying drawings, in which:

FIG. 1 shows an isometric view of a multi-function scale with large-areadisplay, consistent with various aspects of the present disclosure;

FIG. 1A shows an isometric, cross-sectional view of a multi-functionscale with large-area display, consistent with various aspects of thepresent disclosure;

FIGS. 2 and 2-i show top views of a multi-function scale with large-areadisplay, consistent with various aspects of the present disclosure;

FIGS. 3A-D show top views of a number of multi-function scale displays,consistent with various aspects of the present disclosure;

FIG. 4 shows a multi-function scale with large-area display, consistentwith various aspects of the present disclosure;

FIG. 5A is a flow chart illustrating an example manner in which auser-specific physiologic meter/scale may be programmed to providefeatures consistent with aspects of the present disclosure;

FIG. 5B shows current paths through the body for the IPG trigger pulseand Foot IPG, consistent with various aspects of the present disclosure;

FIG. 6 shows an example of the insensitivity to foot placement on scaleelectrodes with multiple excitation and sensing current paths,consistent with various aspects of the present disclosure;

FIG. 7A depicts an example block diagram of circuitry for operating corecircuits and modules, including, for example, those of FIGS. 8A-8B, usedin various specific embodiments of the present disclosure;

FIG. 7B shows an exemplary block diagram depicting the circuitry forinterpreting signals received from electrodes.

FIGS. 8A-8B show example block diagrams depicting the circuitry forsensing and measuring the cardiovascular time-varying IPG raw signalsand steps to obtain a filtered IPG waveform, consistent with variousaspects of the present disclosure;

FIG. 9 shows an example block diagram depicting signal processing stepsto obtain fiducial references from the individual Leg IPG “beats,” whichare subsequently used to obtain fiducials in the Foot IPG, consistentwith various aspects of the present disclosure;

FIG. 10 shows an example flowchart depicting signal processing tosegment individual Foot IPG “beats” to produce an averaged IPG waveformof improved SNR, which is subsequently used to determine the fiducial ofthe averaged Foot IPG, consistent with various aspects of the presentdisclosure;

FIG. 11 shows an example configuration for obtaining the pulse transittime (PTT), using the first IPG as the triggering pulse for the Foot IPGand ballistocardiogram (BCG), consistent with various aspects of thepresent disclosure;

FIG. 12 shows another example of a scale with interleaved footelectrodes to inject and sense current from one foot to another foot,and within one foot, consistent with various aspects of the presentdisclosure;

FIG. 13A shows another example of a scale with interleaved footelectrodes to inject and sense current from one foot to another foot,and to measure Foot IPG signals in both feet, consistent with variousaspects of the present disclosure;

FIG. 13B shows another example of a scale with interleaved footelectrodes to inject and sense current from one foot to another foot,and to measure Foot IPG signals in both feet, consistent with variousaspects of the present disclosure;

FIG. 13C shows another example approach to floating current sources byusing transformer-coupled current sources, consistent with variousaspects of the present disclosure;

FIGS. 14A-D show an example breakdown of a scale with interleaved footelectrodes to inject and sense current from one foot to another foot,and within one foot, consistent with various aspects of the presentdisclosure;

FIG. 15 shows an example block diagram of circuit-based building blocks,consistent with various aspects of the present disclosure;

FIG. 16 shows an example flow diagram, consistent with various aspectsof the present disclosure;

FIG. 17 shows an example scale communicatively coupled to a wirelessdevice, consistent with various aspects of the present disclosure; and

FIGS. 18A-C show example impedance as measured through different partsof the foot based on the foot position, consistent with various aspectsof the present disclosure.

While various embodiments discussed herein are amenable to modificationsand alternative forms, aspects thereof have been shown by way of examplein the drawings and will be described in detail. It should beunderstood, however, that the intention is not to limit the disclosureto the particular embodiments described. On the contrary, the intentionis to cover all modifications, equivalents, and alternatives fallingwithin the scope of the disclosure including aspects defined in theclaims. In addition, the term “example” as used throughout thisapplication is only by way of illustration, and not limitation.

Various aspects of the present disclosure are directed toward amulti-function scale with a large-area display to present results of thescale's multiple sensing functionalities as related to user-fitnesscharacteristics, and may provide other information pertinent to theuser. In many embodiments, the multi-function scale provides a number ofbiometric and physiological measurements. Based on the measurements, acondition or conditions of the user are displayed on the large-areadisplay between or beneath the user's feet.

In some embodiments of the present disclosure, a weighing scale includesa base unit that integrates a support structure, a display,user-targeted circuitry, and a communication driver. The supportstructure has a platform region with sensor circuitry therein, and whichengages a user via the sensor circuitry while the user stands on theplatform region. The sensor circuitry collects physiological data fromthe user such as cardiovascular information pertaining to states ofexertion, which is then forwarded on to the user-targeted circuitry foranalysis. Other physiological data may also be collected, such asmeasurements of body composition. The display displays data through theplatform region, with the data relating to physiological parameters ofthe user as determined by the user targeted circuitry and pertaining toa fitness condition.

The user-targeted circuitry operates in a fitness testing mode byinstructing a user to engage the sensor circuitry on the platform regionof the weighing scale, during respective states of exertion (e.g., in areduced-exertion state and in an elevated-exertion state). The sensorcircuitry collects physiological data from the user indicative offitness characteristics in each state. For instance, the user-targetedcircuitry may instruct the user to engage the sensor circuitry to obtainbaseline physiological characteristics, and later instruct the user toraise or lower his or her heat rate, after which the user is againengaged by the sensor circuitry on the platform region. The sensorcircuitry collects physiological data from the user for each physicalexertion state, which the user-targeted circuitry uses to determinephysiological parameters of the user. Methodologies for determiningphysiological parameters of the user are discussed in more detail below,in reference to FIGS. 5-18C. The communication driver receives theinformation (including the determined physiological parameters) from theuser-targeted circuitry and provides the information to the display forviewing by the user through the platform region. The physiological datathus can be used to provide the user or a medical professional withindications as to their level of physical fitness.

In some embodiments, a weighing scale as characterized above includes adata-access circuit that stores and provides access to user-specificdata including physiological parameters of the user, which areresponsive to or developed by the user-targeted circuitry. Thedata-access circuit may be external to the scale base unit and maycommunicate and share user-specific data with the base unit, as well asother electronic devices associated with the user (e.g., via a wired orwireless communication link). In some specific embodiments, thedetermined physiological parameters of the user are compared tophysiological parameters of the user stored in the data-access circuit,in order to determine changes in physical fitness of the user over time.In one such embodiment, the user-targeted circuitry accesses the storedphysiological parameters of the user in the data-access circuit, andcompares current (sensed) physiological parameters of the user to thestored physiological parameters of the user to provide an indication ofchanges in physical health of the user over time.

In many embodiments, the user may compare his or her physiologicalparameters to a health metric. Some examples of health metrics includephysiological parameters of an average individual of the same sex, age,height, weight, etc., or physiological parameters indicative of a levelof fitness to which the user wishes to achieve (e.g., run a marathon, orsummit Mount Everest). In one specific embodiment, user-targetedcircuitry accesses current physiological parameters of the user and thehealth metric associated with at least one of a number of theuser-specific physiological parameters stored in the data-access circuit(sex, age, height, weight of the user). Current physiological parametersmay, for example, be obtained by sensing physiological data of the userand assessing the physiological parameters of the user, as discussed inmore detail below, or by accessing recent physiological parameters ofthe user stored in a data-access circuit. The user-targeted circuitrythen compares the current physiological parameters to the stored healthmetric to determine a physical fitness condition of the user.

The scale display may present results in a number of ways, such as bydisplaying information in a mode for fitness beginners that simplyindicates “below average,” “average,” and “above average.” In otherembodiments directed to sophisticated fitness enthusiasts, the displaypresents individual physiological parameters of the user, relative tothe associated health metric, and also graphs the user's progress overtime as compared to the particular health metric.

In many embodiments, the fitness scale (including user-targetedcircuitry) determines (and displays) action(s) to encourage improvementof the user's physical fitness, after determining the user's physicalfitness characteristics. For example, where a user's determinedphysiological parameters are indicative of a lack of cardiovascularfitness, the scale may suggest that the user add a one mile jog into hisor her daily fitness routine. In many embodiments, the user-targetedcircuitry may transmit (via the data-access circuit) to externalpersonal electronic devices, associated with the user, the physiologicalparameters, physiological data, recommended physical regimens, and/orother data indicative of the physical health of the user. In suchembodiments, the personal electronic devices may store such data and/orfurther analyze the data in view of other stored data such as dataindicative of diet and caloric intake of the user or the currentphysical regimen of the user. The personal electronic device may theninstruct the user to adjust her or her diet and/or physical regimenaccordingly. In further embodiments, the personal electronic devicestransmits stored data indicative of the diet and caloric intake of theuser, the current physical regimen of the user, or other health relateddata. The user-targeted circuitry may then also consider such data whendetermining the physiological parameters of the user to further improvethe accuracy of such determined physiological parameters.

In one specific embodiment of the scale's fitness testing mode,user-targeted circuitry accesses a data-access circuit to determineprevious recovery times of the user after physical exertion. The scalethen instructs the user to engage sensor circuitry on a platform regionof the scale, after physical exertion, until the user has fullyrecovered to baseline values. The user-targeted circuitry receives thephysiological data from the sensor circuitry indicative of the recoverytime of the user, and compares the current recovery time of the user toprevious recovery times of the user to determine the change in physicalhealth of the user over time.

In various embodiments of the present disclosure, a fitness trackingscale includes a display that receives touch signal data indicative ofengagement of the user on a platform region above the display and theassociated position and movement of the user on the platform region. Thetouch signal data is transmitted to a communication driver whichprocesses the touch signals, and determines the associated position andmovement with such touch signals. Accordingly, the user is able to usetheir feet to make selections on the display, such as selecting aphysiological test to conduct, inputting information relevant to theuser's health, among other activities such as browsing entertainmentrelated data displayed while the scale is conducting a test. In furtherembodiments, the touch signal data may be used by a communication driverof the display. In one such embodiment, the communication driverrecognizes whether the user is standing on the platform region. When thecommunication driver determines the user is not standing on the platformregion, the communication driver presents information via a large-areadisplay mode of the display. When the communication driver determinesthe user is standing on the platform region and, the communicationdriver presents information via a reduced-area display mode in areduced-area display region of the platform region which is adjacent tofeet of the user, when the user is standing on the platform region.

In certain more specific embodiments of the touch-screen displaydiscussed above, the user-targeted circuitry may store data indicativeof a user's foot size, shape and/or other identifying characteristic ina data-access circuit. Accordingly, when an unidentified user engages aplatform region of the scale, the user-targeted circuitry may comparethe unidentified user's foot to user-specific data stored in thedata-access circuit to determine the identity of the user.

Certain embodiments of the present disclosure are directed to theaesthetic appearance of the fitness testing scale when not in use. Inone such embodiment, the scale further includes a camera to captureimage data indicative of an area around the base unit and presence ofthe user. Accompanying image processing circuitry receives the capturedimage data from the camera and determines color and pattern themesassociated with the image data of the area around the base unit, and thepresence of the user; based on the determinations of the imageprocessing circuitry, the display functions in either an active or idlemode. In the active mode, determined by presence of the user by theimage processing circuitry, the display presents information thatcorresponds to the physiological parameters of the user. In the idlemode, determined by non-presence of the user by the image processingcircuitry, the display presents an image indicative of the area aroundthe base unit, based on the image data processed by the image processingcircuitry.

In certain specific embodiments of the present disclosure, after thescale analyzes physiological data of a user and determines the user'sphysiological parameters, such data can be logged and trended (over aperiod of time) with previously recorded physiological data (e.g.,weight and body composition) and stored in a data-access circuit.

In a further embodiment of the present disclosure, in addition tomeasuring a user's baseline physiological/hemodynamic parameters, aspecific fitness-testing mode is invoked. The scale, when put intofitness testing mode, coaches the user to raise his or her heart rateand then measures physiological/hemodynamic parameters of the user (e.g.heart rate, (BCG), heart rate, pulse-wave velocity (PWV), oxygensaturation, etc.), either alone or in combination. In this mode, theuser is instructed by the scale or another linked device (e.g. cellphone), via an audible or visual prompt to step off the scale and raisethe user's heart rate (e.g. go for a run, run up and down stairs,jumping jacks, or do another form of exercise), and then return to thescale. When the user returns to the scale after exercise the user'sheart rate is substantially elevated relative to the user's baseline(resting) values already recorded. The user is instructed to stand onthe scale, while the scale repeatedly measures the user'sphysiological/hemodynamic parameters, including how quickly the userrecovers from physical exertion. In certain embodiments, the user isinstructed to rest and return to the scale after a given amount of time(e.g., the scale may provide an indication of such a time periodexpiring, prompting the user to return to the scale), after which thescale obtains additional physiological measurements. Recovery slopes,time constants or other derived recovery parameters are computed fromthe recorded data and stored. As these parameters are collected andmeasured over a period of time (e.g. days, months, years, etc.) theuser's recovery to a baseline level (or at least slope or time-constantof recovery) can be estimated. By comparing these recover-to-baselineparameters against a population, other health metrics, the user'sbaseline parameters and other historical data, the user's changes infitness levels can be quantified and displayed to the user as feedback.By comparing the user's baseline physiological parameters to the user'sparameters after periods of exercise the scale can provide an analysisover time of the change in the user's physical condition, and therebythe change in the user's overall physical fitness. The scale can alsoprovide trending data (e.g. communicating to the user if they aregetting more or less fit over time). Measurement results can be comparedagainst appropriate population norms or health metrics (e.g. age, raceor gender) and against the user's own short and long-term results.

In another embodiment of the present disclosure, recovery-to-baselineparameters do not need to be measured from a maximum heart rate down toa baseline, alleviating difficulties in obtaining such a measurementwhich can be impractical in terms of the time needed to go from highexertion exercise to a baseline or resting heart rate. In suchinstances, algorithms performing the fitness testing look at changes inthe user's various parameters relative to time, such as by determiningthat a user has recovered substantially enough toward baselineparameters to permit mathematical analysis to yield an estimate ofrecovery over time.

In a further embodiment of the present disclosure the results of thephysiological testing can be displayed on the scale, on a mobile device,personal electronic device (e.g. smart watch or tablet), a computer, ona website, or in another way as desired by the user. The user can inputrelated information such as the user's training regimen, specificexercise plan, diet or food plan, and fitness goals (e.g. run a marathonin a month, lose 10 pounds by a certain date, lower resting heart rate,or increase muscle mass). The scale responds with an algorithmicestimation of desired fitness improvements per unit of time (e.g., day,week, or month).

In a further embodiment of the present disclosure, the fitness testingscale can also be linked to external devices such as pedometers, mobiledevices, other personal electronic devices, or GPS trackers to give thealgorithms access to more information about the fitness state of theuser or the exercise that the user has completed (including the exercisespecifically done to raise the user's heart rate for the fitness testingmode). The fitness testing scale can also log and trend weight and bodycomposition, as these measurements relate to the degree of fitness andto the overall goals of the user (e.g. reducing overall weight or bodyfat percentage).

A further embodiment of the present disclosure is directed to a scalethat works with algorithms that coach the user over time in terms oftraining regimens to achieve specific goals such as, for exampletraining to run a marathon or play soccer. The algorithms may, forexample be embodied in the scale, in the cloud, in a user's mobileelectronic device or computer.

In various embodiments a multi-function scale including a display isdisclosed, the display being effectively the entire top surface of thescale. Support glass above the display transmits the weight of a user toa bezel along the perimeter of the scale (away from the display), whilealso transmitting touch-capacitive signals indicative of a user'sposition and movement on the support glass through the display to scalecircuitry. The bezel houses load cells equally spaced along theperimeter of the scale. Each load cell outputs an electrical signalindicative of a mass transmitted from the user through the load cell tothe scale circuitry. A support frame is attached to the bezel andsupports the display within the bezel. A plurality of translucentelectrode leads are embedded into the support glass to provideelectrical signals to the scale circuitry; the electrical signals areinterpreted by the scale circuitry as being indicative of a condition ofa user, such a condition being presented on the display for the user.

In some embodiments of the present disclosure, a display of amulti-function scale is touch-responsive or tilt-responsive. The displaymay portray simple menus that can be controlled by the user's feet/toes,hands or other body part. A user's feet (or hands) are sensed via touchsensors on the screen or display and the scale can identify the outlineof a user's feet (or hands or other body part). The user's feet (orhands) may provide user input for functional or aesthetic feedback viathe display such as producing animated graphics around the users feet orhands (e.g., simulated lapping surf videos that interact with the user'sfeet or hands; glowing around the user's feet or hands; fish nibbling atthe toes, etc.). A user may also change posture, shifting the weightdistribution over the scale's load cells to provide user input. The userprovided feedback allows for the selection of menu options, testselection, browsing information or articles presented on the display, orthe input of test relevant user data such as age, medical conditions,etc. In various embodiments, the touch-responsive screen indicates toscale circuitry the location of a user's feet relative to a plurality ofelectrodes located across a top surface of the multi-function scale.This permits the processor to select appropriate electrodes for adesignated biometric measurement, based, at least in part, on thereal-time location of the user's feet on the scale.

In further specific embodiments of the present disclosure, amulti-function scale is communicatively coupled with one or more of auser's portable electronic device, an internet router, or other homeelectronic device. The scale communicates and exchanges data with thesedevices for display and control by a user (e.g. using physiologicalparameters to improve a fitness or health condition). In variousembodiments, while the multi-function scale is conducting biometric andphysiological measurements of the user, the user (by way of thetouch-responsive screen) may interact with one or more of the otherdevices. For instance, the user may browse news communicated to themulti-function scale by an internet router, change a station on atelevision or a song playing on a sound system, or review the user'sschedule transmitted to the multi-function scale by the user'ssmartphone. Additionally, while the scale is conducting barometric andphysiological measurements of the user prior to user identification, thedisplay portrays interesting or entertaining information (e.g., surflapping at the user's feet). In yet further implementations of thedisclosure directed to smart-homes, a multi-function scale provides usercontrol (via the touch-screen display) a plurality of other devicesthroughout the home, such as a climate control system, security system,or operation of a shower. The electronic communications between themulti-function scale and the various devices may take the form of eitherwireless or wired communications. Further, a multi-function largedisplay scale can be used to communicate with other scale users eitherusing the same scale unit or another scale in the home or other wirelessor personal electronic devices. For instance, a message or note may beleft, or a meeting or appointment may be confirmed. Further, digitalcommunication and haptic feedback from a smart watch may be implementedto make selections related to scale functionality.

Certain aspects of the present disclosure are directed toward amulti-function scale that obtains a plurality of impedance-measurementsignals while a set of at least three electrodes are concurrentlycontacting a user. Additionally, various aspects of the presentdisclosure include determining a plurality of pulse characteristicsignals based on the plurality of impedance-measurement signals. One ofthe pulse characteristic signals is extracted from one of theimpedance-measurement signals and is used as a timing reference toextract and process another of the pulse characteristic signals. Thesignals obtained by the scale are indicative of a condition of the user,such as percentage: muscle mass percentage, body water percentage, amongothers. The condition of the user is displayed on a large-area displaybeneath the user's feet, along with other information that may bepreprogrammed or requested by the user for display such as time of day,traffic conditions, stock portfolio, weather, as well as a plurality ofother pieces of information that may be collected.

In another embodiment, an apparatus includes a base unit including aplatform area. The apparatus also includes a set of electrodes includinga plurality of electrodes over the platform area for contacting one footof a user and including at least one other electrode configured andarranged for contacting the user at a location along a lower limb (e.g.,other foot) that does not include the one foot. Pulse-processingcircuitry is communicatively coupled to, and configured with, the set ofelectrodes to obtain a plurality of impedance-measurement signals whileeach of the electrodes is concurrently contacting the user and todetermine a plurality of pulse characteristic signals based on theplurality of impedance-measurement signals. At least one of theimpedance-measurement signals is obtained within the one foot andanother of the impedance-measurement signals is obtained between the onefoot and the other location. One of the pulse characteristic signals isextracted from one of the impedance-measurement signals and is used as atiming reference to extract and process another of the pulsecharacteristic signals.

Various aspects of the disclosure are directed to a multi-function scalewith a large-area display. The large-area display may be programmed todisplay aesthetically pleasing screen savers, both when in use, or idle.For example, images, animations, and videos, may be presented on thedisplay with overlaid information (as may be selected by the user). Insome specific embodiments of the present disclosure, where themulti-function scale, and based on its measurements, has determined acondition in the user indicative of increased stress levels (asindicated by high blood pressure, heart rate, etc.), for example; themulti-function scale may display images or video, such as waves lappingover sand and play accompanying sounds or music, among other sensorydevices, intended to calm and sooth the user. In yet furtherembodiments, based on an assessed condition, as indicated by themulti-function scale measurements, the multi-function scale may suggestaudibly or visually (through the scale's display) activities, dietaryrestrictions, or in the case where the indicated condition islife-threatening (e.g., measurements indicating an imminent heart attackor stroke, etc.), call an ambulance for the user. Information may alsobe portrayed on the display of the scale for a period of time when theuser is off the device.

Another embodiment is directed to an apparatus having a base unitincluding a platform area, a set of electrodes and pulse-processingcircuitry. The electrodes include a plurality of electrodes over theplatform area for contacting a user at a limb extremity (being the handor foot) and one or more other electrodes for contacting the user at adifferent location. The pulse-processing circuitry is communicativelycoupled to, and configured with, the set of electrodes to obtain aplurality of impedance-measurement signals while each of the electrodesis concurrently contacting the user and to determine a plurality ofpulse characteristic signals based on the impedance-measurement signals.At least one of the impedance-measurement signals is obtained within thelimb extremity and another of the impedance-measurement signals isobtained between the limb extremity and the other location. One of thepulse characteristic signals is extracted from one of theimpedance-measurement signals and is used as a timing reference toextract and process another of the pulse characteristic signals.

In various embodiments of the present disclosure, a multi-function scaleincludes imaging circuitry such as a camera and image processingcircuitry. Where a camera is implemented, the camera is directed eitherat the floor below the scale or the surrounding area. Based on theimages processed (by the image circuitry) of the area surrounding thescale, the multi-function scale's large-area display depicts an imagethat mimics the surrounding area when idle. For example, in someembodiments, the scale depicts an image indicative of the surface,flooring or floor covering below the scale, enabling the scale to “blendin” to its surroundings, minimizing any detraction of aesthetics thescale would otherwise cause through its visually non-conformingpresence, if desired by the user. In another embodiment of the presentdisclosure, the scale is mountable flush with or inset into a floor inwhich the scale is located. This approach can be used to further enhancethe “blend in” effect of the scale and to facilitate powering via ahardwired voltage connection. The result is that, when themulti-function scale is idle, the scale is effectively camouflaged fromview or at a glance. In other embodiments, the camera may be directed atan upward angle, providing a view of the room in which themulti-function scale is located. Based on image data collected by thecamera and processed by image processing circuitry, the display willpresent the prominent colors and patterns found in the room, minimizingthe aesthetic detraction of the multi-function scale.

In a further embodiment of the present disclosure, a multi-functionscale includes circuitry such as a camera, microphone or imageprocessing circuitry that interacts with an external environmentalsensor. Such an environmental sensor may, for example, be connected to apersonal electronic device to alert a user of motions and sounds in ahouse, or to communicate wirelessly with another individual eithernearby or at a distant location. In some implementations, the scalecommunicates with and relies on an external environmental sensor that iswirelessly connected to the user's home or living environment. Forexample, in one embodiment the external environmental sensors facilitatepower saving by alerting the scale that a user is moving toward thelocation of the scale, thereby prompting the scale to transition (turnon or power up) from idle or reduced-display mode to active orlarge-display mode, identify the user, and begin interacting with theuser. Further, the external environmental sensor can also trigger thescale to turn off or to transition from active mode or large-displaymode to a reduced-display or idle mode, in response to sensing that theuser is leaving the area where the scale is located.

A further embodiment of the present disclosure is directed to a scalethat facilitates power-saving by communicating with a bed orbedroom-based sensor that can trigger the scale to turn on andtransition from idle or reduced-screen-mode to active or large-displaymode when the sensor detects user activity. For instance, by detectingthat user wakes-up and/or gets out of bed, the scale can be activated.

Various other embodiments of the present disclosure include a scale,that when placed near the user's sleeping environment (e.g. bedroom) andcoupled with a sensor located on the user, or in or near the user's bedor bedroom, analyzes and stores the user's sleep patterns, sleepenvironment and climate, and other physiological measurements (e.g.average heart rate, respiratory and breathing rate, movement, etc.) ofthe user while the user is asleep. One benefit of such an embodiment isthat use by the user promotes improved sleep and overall health andwellness. Data obtained while the user is sleeping can be displayed onthe scale or communicated wirelessly to or from other personalelectronic devices or programs for viewing, storage or future analysisby the user.

In a further embodiment of the present disclosure, the scale includes apower source such as a battery that can be charged or rechargedwirelessly (e.g. using a variety of wireless charging modalities suchas: magnetic inductive charging magnetic resonance charging, radio wavecharging, and ultrasound charging). The scale unit may also serve as acharging portal for charging or powering other portable electronicdevices wirelessly.

In one power-saving embodiment of the present disclosure, the scaledisplay is operated in a large-area display mode, where the entirety ofthe surface of the scale platform consists of the display when the useris not standing on the scale; and a smaller or reduced-area displaymode, when the user is standing on the scale (e.g., the portions of thedisplay visible to the user). In some embodiments, only a small portionof the display between the user's feet will continue to displayinformation to the user in the reduced-area display mode, and in otherembodiments the reduced-area display mode turns-off the display areaunder the user's feet to save battery power.

In another power saving embodiment of the disclosure, the scale mayoperate in an active mode, determined by the presence of the user by acamera or microphone integrated onto the scale. When image processingcircuitry associated with the camera senses motion (or the microphonecircuitry detects a noise), the scale enters an active mode and presentsinformation that corresponds to the physiological parameters of the useror other information as may be programmed by the user. In thealternative, idle mode, where the scale has been inactive for aprogrammed period of time, or the image processing circuitry andmicrophone circuitry determine the lack of user presence in the room,the scale may turn-off the display to save power, present an imageindicative of the area around the base unit, or present and image oranimation selected by the user (as may be desired by the user).

In some embodiments of the present disclosure, the scale may be used inconjunction with workout activities. For example, the scale can be usedas a force meter, for exercises involving the feet (e.g., conducting aleg press or military press while standing on the scale). Such meteringwould also be useful for maintaining consistent exerted forces duringballistic exercises and to chart fatigue over repetitions (and to alsocompare to previous workout sessions). In certain implementations, thescale is integrated within exercise equipment to facilitate suchdetection and, for example, to provide an accurate indication of anamount of force actually applied to move weight. In other relatedembodiments, the scale may be used intermittently during a workoutregimen to verify that the regimen (or current exercise) is raising theusers physiological parameters to the appropriate levels for theexercise (e.g., that a cardiovascular exercise, such as jogging, israising the user's heart rate to 80% of its maximum).

The above discussion/summary is not intended to describe each embodimentor every implementation of the present disclosure. The figures anddetailed description that follow also exemplify various embodiments.

Turning now to the figures, FIG. 1 shows an isometric view of amultifunction scale 100 with a large-area display (beneath platformregion 115), consistent with various aspects of the present disclosure.In this particular embodiment, the scale 100 has a primarily rectangularshape with a support structure 110 around the perimeter of the scalethat transfers the weight of a user on the platform region 115 throughload cells in each corner of the support structure 110. The scale 100may, for example, be implemented with circuitry that carries out one ormore of the various fitness-based aspects described herein. It is to beunderstood that the aesthetic design of the multifunction scale 100 maytake on a plurality of shapes and sizes (based on the needs of users,e.g., weight requirements or aesthetic preferences). A feature of themultifunction scale 110 is the large-area display that makes up themajority of the top surface of the scale. The display may present theuser with a myriad of information, such as the results of physiologicaland biometric test results conducted by the scale, entertainmentinformation (while the scale is conducting tests or a weightmeasurement), and aesthetic screen savers.

FIG. 1A shows an isometric, cross-sectional view of a multifunctionscale 100 with a support structure 110 that integrates a large-areadisplay 120, a platform region 115, and circuitry 130 (including atleast user-targeted circuitry, and a communication driver), consistentwith various aspects of the present disclosure. The platform region 115above the display 120 transmits the weight of a user to the supportstructure 110 and away from the display, while also transmittingtouch-capacitive signals indicative of a user's position and/or movementon the platform region 115, through the display, to the scale circuitry130. The support structure 110 is attached to a bezel which supports thedisplay 120. The support structure 110 further houses load cells equallyspaced along the perimeter of the scale 100. Each load cell outputs anelectrical signal indicative of a mass transmitted from the user throughthe load cell to the scale circuitry (which interprets the electricalsignals and presents the weight of the user on the display). In someimplementations, a plurality of translucent electrode leads are embeddedinto the platform region 115 to provide electrical signals to the scalecircuitry 130, and the electrical signals are interpreted by the scalecircuitry 130 as being indicative of a condition of a user, with thecondition being presented on the display 120 for the user. In otherimplementations, different types of sensors (e.g., organicsemiconductors) are implemented with the sensor circuitry.

In an embodiment in accordance with FIG. 1A, a weighing scale 100includes a support structure 110 having a platform region 115 withsensor circuitry therein (e.g., electrodes). The platform region 115engages a user with the sensor circuitry while the user stands on theplatform region 115 and use the sensor circuitry to collectphysiological data from the user. While the user stands on the scale100, the display 120 displays data through and throughout the entireplatform region.

The scale 100 also includes circuitry 130 including user-targetedcircuitry and a communication driver. The user-targeted circuitryreceives the physiological data from the sensor circuitry and determinesphysiological parameters of the user, including a user-weight metric,while the user stands on and engages the sensor circuitry of theplatform region 115. The communication driver provides information fromthe user-targeted circuitry to the display 120 for viewing by the userthrough the platform region 115. In various embodiments, theuser-targeted circuitry operates to communicate with the user toinstruct the user relative to states of physical exertion, to exerciseor rest in order to obtain data from the user under the respectivestates. Such an approach may, for example, be carried out in a manner asdiscussed above.

In some embodiments the circuitry 130 also includes a data-accesscircuit that provides access to user-specific data including storedphysiological parameters of the user in response to or developed by theuser-targeted circuitry and to store physiological parameters of theuser determined by the user-targeted circuitry (in other embodiments,the data-access circuit may be external to the scale 100, and may beaccessed by the circuitry 130 over a communication network).

Load bearing characteristics of the multifunction scale 100 may provideboth functionality and longevity. The platform region 115, inconjunction with the support structure 110 (and the bezel), minimizesthe load transfer to the display 120 while still maintaining sufficientconductivity through the platform region 115 (e.g., a glass platform orother clear material) to the display 120 to allow for touch-screenfunctionality. If the platform region 115 is too compliant, under theuser's weight, excessive force exerted on the display 120 may causedamage. If the platform region 115 is not conductively coupled to thedisplay 120 (e.g., due to a gap there-between), touch-screenfunctionality of the scale 100 may be challenging. Accordingly, FIG. 1Adiscloses one embodiment that addresses such issues via a platformregion 115 that transfer weight to the support structure 110 withminimal compliance, by which the display 120 remains conductivelycoupled to the platform region 115 while preventing excessive force frombeing exerted on the display 120 (that would otherwise cause damage).

In certain specific embodiments of the present disclosure, as shown inFIGS. 2 and 2 i, multifunction scale 200 includes a support structure210 which integrates a large-area display 220 and a platform region 210(where the user will stand when the scale 200 is in use). In such anembodiment, the display 220 is essentially the full length of the scale20, but not full width. This display size is closer in dimensions to atablet computing device (such as an iPad). The sensor circuitry in theplatform region 210 includes electrodes for physiological and biometricsensing.

As discussed in more detail below in reference to FIGS. 3A-D, thedisplay 220 is capable of presenting a myriad of information to theuser, including specific data to encourage the user to use the scale tomonitor exercise and perform certain specific types and/or forms ofexercise (e.g., for a certain period of time, walk fast, run, jog inplace, perform your favorite exercise as stored in the user profile)and/or patterns of exercise (as displayed, e.g., exercising the heartfor intervals with periods of rest in between and one or morerepetitions thereof). These user-specific aspects can be particularlyadvantageous especially with the circuitry in the scale being configuredto wirelessly or in a wired mode, download data from wearable devices(e.g., chest strap, watch, phone) as worn during scale-instructedexercise (and/or even when standing on scale). As such these peripheraldevices can capture details of the scale-noted exercise including heartrate ramp up/down, energy expenditure, etc., and append the scale's ownmeasurements of the user when the user returns to stand on the scale,thereby forming a more complete data set of physiologic response toexercise.

FIG. 3A-D shows top views of a number of multifunction scale displays,consistent with various aspects of the present disclosure. FIG. 3Apresents an exemplary image that may be selected by a user as a “screensaver,” and displayed by the scale, in a large-area display mode 320,when not in use. In further embodiments, the scale, when not in use mayenter “sleep mode” and present or display pleasant still or videoimages, including a slide-show of images selected by the user, such asfamily-photos or other pleasant preferred images or animations. In morespecific embodiments of the present disclosure, a camera iscommunicatively coupled to the multifunction scale and operates withfacial recognition software for identifying the user and greeting theuser (“Hello Bob”). The apparatus may also identify the user based onmultiple measurement characteristics (e.g., weight, body composition,body mass index (BMW), body fat percentage, PWV, etc., alone orcorrelated with additional measurements), and greet the useraccordingly. Based on the identified user, the scale may operate inaccordance with user-specific aspects as may relate to physiology orpreferences such as for a “screen saver.” For instance, biometric andphysiological tests can be conducted, with the test results saved to theidentified user's file (and/or the results sent to a user's doctor forfurther review and analysis), as well as a number of otherfunctionalities, such as playing the user's favorite musical artist andloading the display to present the user with pertinent information.Further, the scale may offer multiple modes that the user may choosebetween to ensure greater accuracy of physiological testing results,such as “athlete mode” for users that are very active.

As shown in FIG. 3B, a relaxing ambience may be provided to the roomwhere the multifunction scale is located, such as by displaying a videoof waves lapping over sand, in a large-area display mode of the display320 (when the user is not standing on the scale). In some embodiments,the scale plays an audio track associated with the video. In FIGS. 3C-D,a reduced-area display mode 321 is utilized when the user is standing onthe scale. In such an embodiment, the display area where the user isstanding, 322 is turned-off as the user's feet prevent the user fromseeing this portion of the screen 322, and the disabling of the displayarea 322 reduces battery consumption of the display 320.

In FIGS. 3B-D, while the scale conducts tests on the user (e.g., weightmeasurements, body fat, biometric and physiological tests (e.g.,ballistocardiogram (BCG) or pulse wave velocity (PWV), etc.) or wheneverthe user desires, the user is able to access other information from thescale such as the user's current weight, pulse rate, and time of day,among other user-configurable information. In further more specificembodiments (as shown in FIGS. 3B-D), the scale displays general oruser-specific information, such as weather conditions, stocks, news,traffic conditions, home climate (e.g., screening air quality, oxygenlevel, temperature), commute times, user's daily schedule, personalreminders, or other information as may be collected by the scale via awired or wireless connection to the internet, or to a smart device(e.g., a hand-held mobile or cellular phone, smart watch or otherwearable electronic device, or tablet) or to fixed computing device(e.g., as a phone or watch). Information displayed on the scale is shownin an appropriately scaled font, composition and orientation to bereadable from a standing position. As shown in FIG. 3D, inimplementations of the disclosure directed to smart-homes, amultifunction scale user controls (via the touch-screen display) aplurality of other devices throughout the home such as a climate controlsystem, security system, operation of the shower, etc. The electroniccommunications between the multifunction scale and the various devicesmay take the form of either wireless or wired communications.

FIG. 4 shows a multifunction scale 400 with large-area display (e.g.,for a bathroom), consistent with various aspects of the presentdisclosure. The multifunction scale 400 includes circuitry, such as acamera and image processing circuitry, and user-targeted circuitry thatoperates to instruct the user for obtaining physiologicalcharacteristics of the user under different states of physical exertion,as characterized herein. The camera may be directed at the floor belowthe scale or the surrounding area. Based on the images processed (by theimage processing circuitry) of the area surrounding the scale, themultifunction scale's large-area display depicts an image that mimicsthe surrounding area when idle. As shown in FIG. 4, the room isprimarily furnished in black and white. The image processing circuitryidentifies this black and white room theme based on the images capturedby the camera and selects a color or combination of colors in a patternor design that would mimic the décor of the room. As a result, the scale400 is more likely to blend into the décor of the room and minimize thelikelihood that the scale 400 will detract from the ambiance. Inembodiments where the camera is directed at the floor, the scale 400depicts an image indicative of the flooring below the scale 400, whichwould similarly minimize any detraction of aesthetics the scale wouldotherwise cast through its visually non-conforming presence. In eitherembodiment discussed above, when the multifunction scale 400 is idle,from a glance the scale 400 is effectively camouflaged. In otherembodiments, the user and/or an interior designer may select a theme forthe display based on the desired look for the room where themultifunction scale 400 is placed.

FIG. 5A is a flow chart depicting an example manner in which a userspecific physiologic meter or scale may be programmed in accordance withthe present disclosure. This flowchart uses a computer processor circuit(or CPU) along with a memory circuit shown herein as user profile memory546A. The CPU operates in a low-power consumption mode, which may be inoff mode or a low-power sleep mode, and at least one other higher powerconsumption mode of operation. As exemplary circuits for transitioningbetween such a low-power and higher power modes, the CPU can beintegrated with presence and/or motion sense circuits, such as a passiveinfrared (PIR) circuit and/or pyro PIR circuit. In a typicalapplication, the PIR circuit provides a constant flow of data indicativeof amounts of radiation sensed in a field of view directed by the PIRcircuit. For instance, the PIR circuit can be installed behind atransparent upper surface of the platform (such as through the displayscreen of the platform apparatus) and installed at an angle so that themotion of the user, as the user approaches the platform apparatus, canbe sensed. Radiation from the user, upon reaching a certain detectablelevel, wakes up the CPU which then transitions from the low-power mode,as depicted in block 540, to a regular mode or active mode of operation.In alternative embodiments, the CPU transitions from the low-power modeof operation in response to another remote/wireless input used as anintrusion to awaken the CPU. In other embodiments, motion can be sensedwith a single integrated microphone or microphone array, to detect thesounds of a user approaching, or user motion can be detected by anaccelerometer integrated in the scale.

Accordingly, from block 540, flow proceeds to block 542 where the useror other presence is sensed as data is received at the platformapparatus. At block 544, the circuitry assesses whether the receiveddata qualifies as requiring a wake up. If not, flow turns to block 540.If however, wake up is required, flow proceeds from block 544 to block546 where the CPU assesses whether a possible previous user hasapproached the platform apparatus. This assessment is performed by theCPU accessing the user profile memory 546A and comparing data storedtherein for one or more such previous users with criteria correspondingto the received data that caused the wake up. Such criteria mightinclude, for example, the time of the day (early morning or latemorning), the pace at which the user approached the platform apparatusas sensed by the motion detection circuitry, the height of the user asindicated by the motion sensing circuitry and/or a camera installed andintegrated with the CPU, and/or more sophisticated bio-metric dataprovided by the user and/or automatically by the circuitry in theplatform apparatus.

As discussed herein, such sophisticated circuitry can include one ormore of the following user-specific attributes: foot length, type offoot arch, weight of user, manner and speed at which the user steps ontothe platform apparatus, and/or sounds made by the user's motion or byspeech. As is also conventional, facial or body-feature recognition maybe used in connection with the camera and comparisons of imagestherefrom to images in the user profile memory.

From block 546, flow proceeds to block 548 where the CPU obtains and/orupdates user corresponding data in the user profile memory. As alearning program is developed in the user profile memory, each accessand use of the platform apparatus is used to expand on the data andprofile for each such user. From block 548, flow proceeds to block 550where a decision is made regarding whether the set of electrodes at theupper surface of the platform is ready for the user, which may be basedon the data obtained from the user profile memory. For example, delaysmay ensue from the user moving his or her feet about the upper surfaceof the platform apparatus, as may occur while certain data is beingretrieved by the CPU (whether internally or from an external source suchas a program or configuration data updates from the Internet cloud) orwhen the user has stepped over a certain area configured for providingdisplay information back to the user. If the electrodes are not readyfor the user, flow proceeds from block 550 to block 552 to accommodatethis delay.

Once the CPU determines that the electrodes are ready for use while theuser is standing on the platform surface, flow proceeds to block 560.Stabilization of the user on the platform surface may be ascertained byinjecting current through the electrodes via the interleaved arrangementthereof. Where such current is returned via other electrodes for aparticular foot and/or foot size, and is consistent for a relativelybrief period of time (e.g., a few seconds), the CPU can assume that theuser is standing still and ready to use the electrodes and relatedcircuitry.

At block 560, a decision is made that both the user and the platformapparatus are ready for measuring impedance and certain segments of theuser's body, including at least one foot.

The remaining flow of FIG. 5A includes the application and sensing ofcurrent through the electrodes for finding the optimal electrodes (562)and for performing impedance measurements (block 564). Thesemeasurements are continued until completed at block 566 and all suchuseful measurements are recorded and are logged in the user profilememory for this specific user, at block 568. At block 572, the CPUgenerates output data to provide feedback as to the completion of themeasurements and, as maybe indicated as a request via the user profilefor this user, as an overall report on the progress for the userrelative to previous measurements made for this user and that are storedin the user profile memory. Such feedback may be shown on the display,through a speaker with co-located apertures in the platform's housingfor audible reception by the user, and/or by vibration circuitry which,upon vibration under control of the CPU, the user can sense through oneor both feet while standing on the scale. From this output at block 572,flow returns to the low-power mode as indicated at block 574 with thereturn to the beginning of the flow at block 540.

FIG. 5B shows current paths 500 through the body of a user 505 standingon a scale 510 for the IPG trigger pulse and Foot IPG, consistent withvarious aspects of the present disclosure. Impedance measurements 515are measured when the user 505 is standing and wearing clothing articlesover the feet such as socks or shoes, within the practical limitationsof capacitive-based impedance sensing, with energy limits consideredsafe for human use. The measurements 515 can also be made withnon-clothing material placed between the user's bare feet and contactelectrodes, such as thin films or sheets of plastic, glass, paper or waxpaper, whereby the electrodes operate within energy limits consideredsafe for human use. The IPG measurements also can be sensed in thepresence of callouses on the user's feet that normally diminish thequality of the signal.

As shown in FIG. 5B, the user 505 is standing on a scale 510, where thetissues of the user's body will be modeled as a series of impedanceelements, and where the time-varying impedance elements change inresponse to cardiovascular and non-cardiovascular movements of the user.ECG and IPG measurements can be sensed through the feet and can bechallenging to take due to small impedance signals with (1) low SNR, andbecause they are (2) frequently masked or distorted by other electricalactivity in the body such as the muscle firings in the legs to maintainbalance. The human body is unsteady while standing still, and constantchanges in weight distribution occur to maintain balance. As such,cardiovascular signals that are measured with weighing scale-basedsensors typically yield signals with poor SNR, such as the Foot IPG andstanding BCG. Thus, such scale-based signals require a stable and highquality synchronous timing reference, to segment individualheartbeat-related signals for signal averaging to yield an averagedsignal with higher SNR versus respective individual measurements.

The ECG can be used as the reference (or trigger) signal to segment aseries of heartbeat-related signals measured by secondary sensors(optical, electrical, magnetic, pressure, microwave, piezo, etc.) foraveraging a series of heartbeat-related signals together, to improve theSNR of the secondary measurement. The ECG has an intrinsically high SNRwhen measured with body-worn gel electrodes, or via dry electrodes onhandgrip sensors. In contrast, the ECG has a low SNR when measured usingfoot electrodes while standing on said scale platforms; unless the useris standing perfectly still to eliminate electrical noises from the legmuscles firing due to body motion. As such, ECG measurements at the feetwhile standing are considered to be an unreliable trigger signal (lowSNR). Therefore, it is often difficult to obtain a reliablecardiovascular trigger reference timing when using ECG sensorsincorporated in base scale platform devices. Both Inan, et al. (IEEETransactions on Information Technology in Biomedicine, 14:5, 1188-1196,2010) and Shin, et al. (Physiological Measurement, 30, 679-693, 2009)have shown that the ECG component of the electrical signal measuredbetween the two feet while standing was rapidly overpowered by theelectromyogram (EMG) signal resulting from the leg muscle activityinvolved in maintaining balance.

The accuracy of cardiovascular information obtained from weighing scaleplatforms is also influenced by measurement time. The number of beatsobtained from heartbeat-related signals for signal averaging is afunction of measurement time and heart rate. The Mayo Clinic cites thattypical resting heart rates range from 60 to 100 beats per minute.Therefore, short signal acquisition periods may yield a low number ofbeats to average, which may cause measurement uncertainty, also known asthe standard error in the mean (SEM). SEM is the standard deviation ofthe sample mean estimate of a population mean. Where, SE is the standarderror in the samples N, which is related to the standard error or thepopulation S.

${SE} = \frac{S}{\sqrt{N}}$

For example, a five second signal acquisition period may yield a maximumof five to eight beats for ensemble averaging, while a 10 second signalacquisition could yield 10-16 beats. However, the number of beatsavailable for averaging and SNR determination is usually reduced for thefollowing factors; (1) truncation of the first and last ensemble beat inthe recording by the algorithm, (2) triggering beats falsely missed bytriggering algorithm, (3) cardiorespiratory variability, (4) excessivebody motion corrupting the trigger and Foot IPG signal, and (5) loss offoot contact with the measurement electrodes.

Sources of noise can require multiple solutions for overall SNRimprovements for the signal being averaged. Longer measurement timesincrease the number of beats lost to truncation, false missedtriggering, and excessive motion. Longer measurement times also reducevariability from cardiorespiratory effects. Therefore, if shortermeasurement times (e.g., less than 30 seconds) are desired forscale-based sensor platforms, sensing improvements need to tolerate bodymotion and loss of foot contact with the measurement electrodes.

The human cardiovascular system includes a heart with four chambers,separated by valves that return blood to the heart from the venoussystem into the right side of the heart, through the pulmonarycirculation to oxygenate the blood, which then returns to the left sideof the heart, where the oxygenated blood is pressurized by the leftventricles and is pumped into the arterial circulation, where blood isdistributed to the organs and tissues to supply oxygen. Thecardiovascular or circulatory system is designed to ensure maintenanceof oxygen availability and is often the limiting factor for cellsurvival. The heart normally pumps five to six liters of blood everyminute during rest and maximum cardiac output during exercise canincrease up to seven-fold, by modulating heart rate and stroke volume.The factors that affect heart rate include the degree of autonomicinnervation, fitness level, age and hormones. Factors affecting strokevolume include heart size, fitness level, contractility or pre-ejectionperiod, ejection duration, preload or end-diastolic volume, andafterload or systemic resistance. The cardiovascular system isconstantly adapting to maintain a homeostasis (set point) that minimizesthe work done by the heart to maintain cardiac output. As such, bloodpressure is continually adjusting to minimize work demands during rest.Cardiovascular disease encompasses a variety of abnormalities in (orthat affect) the cardiovascular system that degrade the efficiency ofthe system, which include but are not limited to chronically elevatedblood pressure, elevated cholesterol levels, edema, endothelialdysfunction, arrhythmias, arterial stiffening, atherosclerosis, vascularwall thickening, stenosis, coronary artery disease, heart attack,stroke, renal dysfunction, enlarged heart, heart failure, diabetes,obesity and pulmonary disorders.

Each cardiac cycle results in a pulse of blood being delivered into thearterial tree. The heart completes cycles of atrial systole, deliveringblood to the ventricles, followed by ventricular systole deliveringblood into the lungs and the systemic arterial circulation, where thediastole cycle begins. In early diastole the ventricles relax and fillwith blood, then in mid-diastole the atria and ventricles are relaxedand the ventricles continue to fill with blood. In late diastole, thesinoatrial node (the heart's pacemaker) depolarizes then contracts theatria, the ventricles are filled with more blood and the depolarizationthen reaches the atrioventricular node and enters the ventricular side,beginning the systole phase. The ventricles contract, and the blood ispumped from the ventricles to the arteries.

The ECG is the measurement of the heart's electrical activity and can bedescribed in five phases. The P-wave represents atrial depolarization,the PR interval is the time between the P-wave and the start of the QRScomplex. The QRS wave complex represents ventricular depolarization. TheQRS complex is the strongest wave in the ECG and is frequently used asthe de facto timing reference for the cardiovascular cycle. Atrialrepolarization is masked by the QRS complex. The ST interval thenfollows which represents the period of zero potential betweenventricular depolarization and repolarization. The cycle concludes withthe T-wave representing ventricular repolarization.

The blood ejected into the arteries creates vascular movements due tothe blood's momentum. The blood mass ejected by the heart first travelsheadward in the ascending aorta and travels around the aortic arch thentravels down the descending aorta. The diameter of the aorta increasessignificantly during the systole phase due to the high compliance (lowstiffness) of the aortic wall. Blood traveling in the descending aortathen bifurcates in the iliac branch, which then transitions into astiffer arterial region due to the muscular artery composition of theleg arteries. The blood pulsation continues down the leg and foot. Allalong the way, the arteries branch into arteries of smaller diameteruntil reaching the capillary beds where the pulsatile blood flow turnsinto steady blood flow, delivering oxygen to the tissues. The blood thenreturns to the venous system terminating in the vena cava, where bloodreturns to the right atrium of the heart for the subsequent cardiaccycle.

Surprisingly, high quality simultaneous recordings of the Leg IPG andFoot IPG are attainable in a practical manner (e.g., a user operatingthe device correctly simply by standing on the impedance body scale footelectrodes), and can be used to obtain reliable trigger fiducial timingsfrom the Leg IPG signal. This acquisition can be far less sensitive tomotion-induced noise from the Leg EMG that often compromises Leg ECGmeasurements. Furthermore, it has been discovered that interleaving thetwo Kelvin electrode pairs for a single foot results in a design that isinsensitive to foot placement within the boundaries of the overallelectrode area. As such, the user is no longer constrained to complywith accurate foot placement on conventional single foot Kelvinarrangements, which are highly prone to introducing motion artifactsinto the IPG signal, or result in a loss of contact if the foot isslightly misaligned. Interleaved designs begin when one or moreelectrode surfaces cross over a single imaginary boundary lineseparating an excitation and sensing electrode pair. The interleaving isconfigured to maintain uniform foot surface contact area on theexcitation and sensing electrode pair, regardless of the positioning ofthe foot over the combined area of the electrode pair.

Various aspects of the present disclosure include a weighing scaleplatform (e.g., scale 110) of an area sufficient for an adult of averagesize to stand comfortably still and minimize postural swaying. Thenominal scale length (same orientation as foot length) is 12 inches andthe width is 12 inches. The width can be increased to be consistent withthe feet at shoulder width or slightly broader (e.g., 14 to 18 inches,respectively).

FIG. 6 shows an example of the insensitivity to foot placement 600 onscale electrode pairs 605/610 with multiple excitation paths 620 andsensing current paths 615, consistent with various aspects of thepresent disclosure. An aspect of the platform is that it has a thicknessand strength to support a human adult of at least 200 pounds withoutfracturing, and another aspect of the device platform is comprised of atleast six electrodes, where the first electrode pair 605 is solid andthe second electrode pair 610 is interleaved. Another aspect is that thefirst and second interleaved electrode pairs 605/610 are separated by adistance of at least 40+/−5 millimeters, where the nominal separation ofless than 40 millimeters has been shown to degrade the single Foot IPGsignal. Another key aspect is the electrode patterns are made frommaterials with low resistivity such as stainless steel, aluminum,hardened gold, ITO, index matched ITO (IMITO), carbon printedelectrodes, conductive tapes, silver-impregnated carbon printedelectrodes, conductive adhesives, and similar materials with resistivitylower than 300 ohms/sq. In the certain embodiments, the resistivity isbelow 150 ohms/sq. The electrodes are connected to the electroniccircuitry in the scale by routing the electrodes around the edges of thescale to the surface below, or through at least one hole in the scale(e.g., a via hole).

Suitable electrode arrangements for dual Foot IPG measurements can berealized in other embodiments. In certain embodiments, the interleavedelectrodes are patterned on the reverse side of a thin piece (e.g., lessthan 2 mm) of high-ion-exchange (HIE) glass, which is attached to ascale substrate and used in capacitive sensing mode. In certainembodiments, the interleaved electrodes are patterned onto a thin pieceof paper or plastic which can be rolled up or folded for easy storage.In certain embodiments, the interleaved electrodes are integrated ontothe surface of a tablet computer for portable IPG measurements. Incertain embodiments, the interleaved electrodes are patterned onto akapton substrate that is used as a flex circuit.

In certain embodiments, the scale area has a length of 10 inches with awidth of eight inches for a miniature scale platform. Alternatively, thescale may be larger (up to 36 inches wide) for use in bariatric classscales. In certain embodiments, the scale platform with interleavedelectrodes is incorporated into a floor tile that can be incorporatedinto a room such as a bathroom. In certain embodiments, the scale foldsin half with a hinge for improved portability and storage.Alternatively, the scale platform is comprised of two separable halves,one half for the left foot and the other half for the right foot, forimproved portability and storage. In certain embodiments for ambulatorymeasurements, the interleaved excitation and sensing electrode pairs areincorporated into a shoe insert for the detection of heart rate and acorresponding pulse arrival time (PAT). Alternatively, the interleavedexcitation and sensing electrode pairs are incorporated into a pair ofsocks, to be worn for the detection of heart rate and a correspondingPAT.

In the present disclosure, the leg and foot impedance measurements canbe simultaneously carried out using a multi-frequency approach, in whichthe leg and foot impedances are excited by currents modulated at twodifferent frequencies, and the resulting voltages are selectivelymeasured using a synchronous demodulator. This homodyning approach canbe used to separate signals (in this case, the voltage drop due to theimposed current) with very high accuracy and selectivity.

This measurement configuration is based on a four-point configuration inorder to minimize the impact of the contact resistance between theelectrode and the foot, a practice well-known in the art of impedancemeasurement. In this configuration the current is injected from a set oftwo electrodes (the “injection” and “return” electrodes), and thevoltage drop resulting from the passage of this current through theresistance is sensed by two separate electrodes (the “sense”electrodes), usually located in the path of the current. Since the senseelectrodes are not carrying any current (by virtue of their connectionto a high-impedance differential amplifier), the contact impedance doesnot significantly alter the sensed voltage.

In order to sense two distinct segments of the body (the legs and thefoot), two separate current paths are defined by way of electrodepositioning. Therefore two injection electrodes are used, each connectedto a current source modulated at a different frequency. The injectionelectrode for leg impedance is located under the plantar region of theleft foot, while the injection electrode for the Foot IPG is locatedunder the heel of the right foot. Both current sources share the samereturn electrode located under the plantar region of the right foot.This is an illustrative example; other configurations may be used.

The sensing electrodes can be localized so as to sense the correspondingsegments. Leg IPG sensing electrodes are located under the heels of eachfoot, while the two foot sensing electrodes are located under the heeland plantar areas of the right foot. The inter-digitated nature of theright foot electrodes ensures a four-point contact for proper impedancemeasurement, irrespective of the foot position, as already explained.

FIG. 7A depicts an example block diagram of circuitry for operating corecircuits and modules of the multi-function scale, used in variousspecific embodiments of the present disclosure. Consistent with yetfurther embodiments of the present disclosure, FIG. 7A depicts anexample block diagram of circuitry for operating core circuits andmodules, including, for example, the operation of a CPU with the relatedand more specific circuit blocks/modules in FIGS. 8A-8B. As shown in thecenter of FIG. 7A, the main computer circuit 770 is shown with otherpreviously-mentioned circuitry in a generalized manner without showingsome of the detailed circuitry such as for amplification and currentinjection/sensing (772). The computer circuit 770 can be used as acontrol circuit with an internal memory circuit for causing, processingand/or receiving sensed input signals as at block 772. As discussed,these sensed signals can be responsive to injection current and/or thesesignals can be sensed at least for initially locating positions of thefoot or feet on the platform area, by less complex grid-based sensecircuitry surrounding the platform area as is conventional in capacitivetouch-screen surfaces which, in certain embodiments, the platform areaincludes.

As noted, the memory circuit can be used not only for the user profilememory, but also to provide configuration and/or program code and/orother data such as user-specific data from another authorized sourcesuch as from a user monitoring his/her logged data and/or profile from aremote desk-top. The remote device or desktop can communicate with andaccess such data via a wireless communication circuit 776 via a wirelessmodem, router, ISDN channel, cellular systems, Bluetooth and/or otherbroadband pathway or private channel. For example, the wirelesscommunication circuit 776 can provide an interface between an app on theuser's cellular telephone/tablet (e.g., phablet, IPhone and/or IPad) andthe platform apparatus, wherefrom the IPhone can be the output/inputinterface for the platform (scale) apparatus including, for example, anoutput display, speaker and/or microphone, and vibration circuitry; eachof these I/O aspects and components being discussed herein in connectionwith other example embodiments.

A camera 778 and image encoder circuit 780 (with compression and relatedfeatures) can also be incorporated as an option. As discussed above, theweighing scale components, as in block 782, are also optionally includedin the housing which encloses and/or surrounds the platform apparatus.

For long-lasting battery life in the platform apparatus (batteries notshown), at least the CPU 770, the wireless communication circuit 776,and other current draining circuits are inactive unless and untilactivated in response to the intrusion/sense circuitry 788. As shown,one specific implementation employs a Conexant chip (e.g., CX93510) toassist in the low-power operation. This type of circuitry isspecifically designed for motion sensors configured with a camera forvisual verification and image and video monitoring applications (such asby supporting JPEG and MJPEG image compression and processing for bothcolor and black and white images). When combined with an external CMOSsensor, the chip retrieves and stores compressed JPEG and audio data inan on-chip memory circuit (e.g., 256 KB/128 KB frame buffer) so as toalleviate the necessity of external memory. The chip uses a simpleregister set via the microprocessor interface and allows for wideflexibility in terms of compatible operation with anothermicroprocessor.

In one specific embodiment, a method of using the platform with theplurality of electrodes concurrently contacting a limb of the user,includes operating such to automatically obtain measurement signals fromthe plurality of electrodes. As noted above, these measurement signalsmight initially be through less-complex (e.g., capacitive grid-type)sense circuitry. Before or while obtaining a plurality of measurementsignals by operating the circuitry, the signal-sense circuitry 788 isused to sense wireless-signals indicative of the user approaching theplatform and, in response, cause the CPU circuitry 770 to transitionfrom a reduced power-consumption mode of operation and at least onehigher power-consumption mode of operation. After the circuitry isoperating in the higher power-consumption mode of operation, the CPUaccesses the user-corresponding data stored in the memory circuit andthereafter causes a plurality of impedance-measurement signals to beobtained by using the plurality of electrodes while they are contactingthe user via the platform; therefrom, the CPU generates signalscorresponding to cardiovascular timings of the user, and suchphysiological measurements are communicated via the display.

This method can employ the signal-sense circuit as a passive infrareddetector and with the CPU programmed (as a separate module) to evaluatewhether radiation from the passive infrared detector is indicative of ahuman. For example, sensed levels of radiation that would correspond toa live being that has a size which is less than a person of a three-footheight, and/or not being sensed as moving for more than a coupleseconds, can be assessed as being a non-human.

Accordingly, should the user be recognized as human, the CPU isactivated and begins to attempt the discernment process of which usermight be approaching. This is performed by the CPU accessing theuser-corresponding data stored in the memory circuit (the user profilememory). If the user is recognized based on parameters such as discussedabove (e.g., time of morning, speed of approach, etc.), the CPU can alsoselect one of a plurality of different types of user-discerniblevisual/audible/tactile information and for presenting the discerned userwith visual/audible/tactile information that was retrieved from thememory as being specific to the user. For example, user-selectedvisual/audible data can be outputted for the user. Also, responsive tothe motion detection indication, the camera can be activated to captureat least one image of the user while the user is approaching theplatform (and/or while the user is on the platform to log confirmationof the same user with the measured impedance information). As shown inblock 774 of FIG. 7A, where a speaker is also integrated with the CPU,the user can simply command the platform apparatus to start the processand activation would accordingly proceed.

In another such method, the circuitry of FIG. 7A is used with theplurality of electrodes being interleaved and engaging the user, as acombination weighing scale (via block 782) and a physiologicuser-specific impedance-measurement device. By using theimpedance-measurement signals and obtaining at least twoimpedance-measurement signals between one foot of the user and anotherlocation of the user, the interleaved electrodes assist the CPU inproviding measurement results that indicate one or more of the followinguser-specific attributes as being indicative or common to the user: footimpedance, foot length, and type of arch, and wherein one or more of theuser-specific attributes are accessed, by being read or stored, in thememory circuit and identified as being specific to the user. Thisinformation can be later retrieved by the user, medical and/or securitypersonnel, according to a data-access authorization protocol as might beestablished upon initial configuration for the user.

FIG. 7B shows an exemplary block diagram depicting the circuitry forinterpreting signals received from electrodes. The input electrodes 705transmit various electrical signals through the patient's body(depending on the desired biometric and physiological test to beconducted) and output electrodes 710 receive the modified signal asaffected by a user's electrical impedance 715. Once received by theoutput electrodes 710, the modified signal is processed by processorcircuitry 701 based on the selected test. Signal processing conducted bythe processor circuitry 701 is discussed in more detail below (withregard to FIGS. 8A-B). In certain embodiments of the present disclosure,the circuitry within 701 is provided by Texas Instruments part #AFE4300.

FIGS. 8A-8B show example block diagrams depicting the circuitry forsensing and measuring the cardiovascular time-varying IPG raw signalsand steps to obtain a filtered IPG waveform, consistent with variousaspects of the present disclosure. The example block diagrams shown inFIGS. 8A-8B are separated into a leg impedance sub-circuit 800 and afoot impedance sub-circuit 805.

Excitation is provided by way of an excitation waveform circuit 810. Theexcitation waveform circuit 810 provides an excitation signal by way ofvarious types of frequency signals (as is shown in FIG. 8A) or, morespecifically, a square wave signal (as shown in FIG. 8B). As is shown inFIG. 8B, the square wave signal is a 5 V at a frequency between 15,625Hz and 1 MHz is generated from a quartz oscillator (such as an ECS-100ACfrom ECS International, Inc.) divided down by a chain of toggleflip-flops (e.g. a CD4024 from Texas Instruments, Inc.), each dividingstage providing a frequency half of its input (i.e., 1 Mhz, 500 kHz, 250kHz, 125 kHz, 62.5 kHz, 31.250 kHz and 15.625 kHz). This (square) waveis then AC-coupled, scaled down to the desired amplitude and fed to avoltage-controlled current source circuit 815. The generated current ispassed through a decoupling capacitor (for safety) to the excitationelectrode, and returned to ground through the return electrode(grounded-load configuration). Amplitudes of 1 and 4 mA peak-to-peak aretypically used for Leg and Foot IPGs, respectively.

The voltage drop across the segment of interest (legs or foot) is sensedusing an instrumentation differential amplifier (e.g., Analog DevicesAD8421) 820. The sense electrodes on the scale are AC-coupled to theinput of the differential amplifier 820 (configured for unity gain), andany residual DC offset is removed with a DC restoration circuit (asexemplified in Burr-Brown App Note Application Bulletin, SBOA003, 1991,or Burr-Brown/Texas Instruments INA 118 datasheet).

The signal is then demodulated with a synchronous demodulator circuit825. The demodulation is achieved in this example by multiplying thesignal by 1 or −1 synchronously with the current excitation. Suchalternating gain is provided by an operational amplifier and an analogswitch (SPST), such as an ADG442 from Analog Devices). Morespecifically, the signal is connected to both positive and negativeinputs through 10 kOhm resistors. The output is connected to thenegative input with a 10 kOhm resistor as well, and the switch isconnected between the ground and the positive input. When open, the gainof the stage is unity. When closed (positive input grounded), the stageacts as an inverting amplifier of the gain −1. Alternatively, otherdemodulators such as analog multipliers or mixers can be used.

Once demodulated, the signal is band-pass filtered (0.4-80 Hz) with afirst-order band-pass filter circuit 830 before being amplified with again of 100 with a non-inverting amplifier circuit 835 (e.g., using anLT1058 operational amplifier from Linear Technologies). The amplifiedsignal is further amplified by 10 and low-pass filtered (cut-off at 30Hz) using a low-pass filter circuit 840 such as 2-pole Sallen-Key filterstage with gain. The signal is then ready for digitization and furtherprocessing. In certain embodiments, the amplified signal can be passedthrough an additional low-pass filter circuit 845 to determine body orfoot impedance.

In certain embodiments, the generation of the excitation voltage signal,of appropriate frequency and amplitude, is carried out by amicrocontroller, such as MSP430 (Texas Instruments, Inc.). The voltagewaveform can be generated using the on-chip timers and digitalinput/outputs or pulse width modulation (PWM) peripherals, and scaleddown to the appropriate voltage through fixed resistive dividers, activeattenuators/amplifiers using on-chip or off-chip operational amplifiers,as well as programmable gain amplifiers or programmable resistors.Alternatively, the waveforms can be directly generated by on- oroff-chip digital-to-analog converters (DACs).

In certain embodiments, the shape of the excitation is not square, butsinusoidal. Such configuration would reduce the requirements onbandwidth and slew rate for the current source and instrumentationamplifier. Harmonics, potentially leading to higher electromagneticinterference (EMI), would also be reduced. Such excitation may alsoreduce electronics noise on the circuit itself. Lastly, the lack ofharmonics from sine wave excitation may provide a more flexibleselection of frequencies in a multi-frequency impedance system, asexcitation waveforms have fewer opportunities to interfere between eachother. Due to the concentration of energy in the fundamental frequency,sine wave excitation could also be more power-efficient.

In certain embodiments, the shape of the excitation is not square, buttrapezoidal. While not as optimal as a sinusoidal wave, trapezoidalwaves (or square waves whose edges have been smoothed out by a limitedbandwidth or slew rate) still provide an advantage in term of EMI andelectronic noise due to the reduced harmonics.

To further reduce potential EMI, other strategies may be used, such asby dithering the square wave signal (i.e., introducing jitter in theedges following a fixed or random pattern) which leads to so-calledspread spectrum signals, in which the energy is not localized at onespecific frequency (or a set of harmonics), but rather distributedaround a frequency (or a set of harmonics). An example of aspread-spectrum circuit suitable for Dual-IPG measurement is shown inFIG. 8B. Because of the synchronous demodulation scheme, phase-to-phasevariability introduced by spread-spectrum techniques will not affect theimpedance measurement. Such a spread-spectrum signal can be generatedby, but not limited to, specialized circuits (e.g., Maxim MAX31C80,SiTime SiT9001), or generic microcontrollers (see Application ReportSLAA291, Texas Instruments, Inc.). These spread-spectrum techniques canbe combined with clock dividers to generate lower frequencies as well.

As may be clear to one skilled in the art, these methods of simultaneousmeasurement of impedance in the leg and foot can be used for standardBody Impedance Analysis (BIA), with the aim of extracting relativecontent of total water, free-water, fat mass and others. Impedancemeasurements for BIA are typically done at frequencies ranging fromkilohertz up to several megahertz. The multi-frequency measurementmethods described above can readily be used for such BIA, provided thecircuit can be modified so that the DC component of the impedance is notcanceled by the instrumentation amplifier (no DC restoration circuitused). The high-pass filter can be implemented after the instrumentationamplifier, enabling the measurement of the DC component used for BIA.This multi-frequency technique can also be combined with traditionalsequential measurements often used for BIA, in which the impedance ismeasured at several frequencies sequentially. These measurements can berepeated in several body segments for segmental BIAs, using a switchmatrix to drive the current into the desired body segments.

While FIG. 6 shows a circuit and electrode configuration suitable tomeasure two different segments (legs and one foot), this approach is notreadily extendable to more segments due to the shared current returnelectrode (ground). To overcome this limitation, and in particular toprovide simultaneous measurements in both feet, the system can beaugmented with analog switches to provide time-multiplexing of theimpedance measurements in the different segments. This multiplexing caneither be a one-time sequencing (each segment is measured once), orinterleaved at a high-enough frequency so that the signal can besimultaneously measured on each segment. The minimum multiplexing ratefor proper reconstruction is twice the bandwidth of the measured signal,based on signal processing theory, which equals to about 100 Hz for theimpedance signal considered here. The rate must also allow for thesignal path to settle in between switching, usually limiting the maximummultiplexing rate. Referring to FIG. 13A, one cycle might start themeasurement of the leg impedance and left foot impedances (similarly topreviously described, sharing a common return electrode), but thenfollow with a measurement of the right foot after reconfiguring theswitches. Typical switch configurations for the various measurements areshown in the table below.

Switch #1 Switch #2 Switch #3 Switch #4 (Sw1) (Sw2) (Sw3) (Sw4) Legs A Aor B A or B A Right Foot A A or B B A Left Foot B B A or B B

Since right and left feet are measured sequentially, one should notethat a unique current source (at the same frequency) may be used tomeasure both, providing that the current source is not connected to thetwo feet simultaneously through the switches, in which case the currentwould be divided between two paths. One should also note that afully-sequential measurement, using a single current source (at a singlefrequency) successively connected to the three different injectionelectrodes, could be used as well, with the proper switch configurationsequence (no split current path).

In certain embodiments, the measurement of various body segments, and inparticular the legs, right foot and left foot, is achievedsimultaneously due to as many floating current sources as segments to bemeasured, running at separate frequency so they can individually bedemodulated. Such configuration is exemplified in FIG. 13B for threesegments (legs, right and left feet). Such configuration has theadvantage to provide true simultaneous measurements without the addedcomplexity of time-multiplexing/demultiplexing, and associated switchingcircuitry. An example of such floating current source can be found inPlickett, et al., Physiological Measurement, 32 (2011). Another approachto floating current sources is the use of transformer-coupled currentsources (as depicted in FIG. 13C). Using transformers to inject currentinto the electrodes enables the use of simpler, grounded-load currentsources on the primary, while the electrodes are connected to thesecondary. Turn ratio would typically be 1:1, and since frequencies ofinterest for impedance measurement are typically in the 10-1000 kHz(occasionally 1 kHz for BIA), relatively small transformers can be used.In order to limit the common mode voltage of the body, one of theelectrodes in contact with the foot can be grounded.

While certain embodiments presented in the above specification have usedcurrent sources for excitation, it should be clear to a person skilledin the art that the excitation can also be performed by a voltagesource, where the resulting injection current is monitored by a currentsense circuit so that impedance can still be derived by the ratio of thesensed voltage (on the sense electrodes) over the sensed current(injected in the excitation electrodes).

It should be noted that broadband spectroscopy methods could also beused for measuring impedances at several frequencies. Such technique hasthe advantage of lower EMI and simultaneous measurement of impedances atnumerous frequencies. These methods typically use a chirp signal, anoise signal or an impulse signal to excite the load (impedance) at manyfrequencies simultaneously, while sampling the resulting response athigh frequency so as to allow the computation (usually in the frequencydomain) of the impedance over the desired frequency range. Combined withtime-multiplexing and current switching described above, multi-segmentbroadband spectroscopy can be readily achieved.

Various aspects of the present disclosure are directed toward robusttiming extraction of the blood pressure pulse in the foot which isachieved by means of a two-step processing. In a first step, the usuallyhigh-SNR Leg IPG is used to derive a reference (trigger) timing for eachheart pulse. In a second step, a specific timing in the lower-SNR FootIPG is extracted by detecting its associated feature within a restrictedwindow of time around the timing of the Leg IPG. Such guided detectionleads to a naturally more robust detection of foot timings.

FIG. 9 shows an example block diagram depicting signal processing stepsto obtain fiducial references from the individual Leg IPG “beats,” whichare subsequently used to obtain fiducials in the Foot IPG, consistentwith various aspects of the present disclosure. In the first step, asshown in block 900, the Leg IP and the Foot IPG are simultaneouslymeasured. As shown at 905, the Leg IPG is low-pass filtered at 20 Hzwith an 8-pole Butterworth filter, and inverted so that pulses have anupward peak. The location of the pulses is then determined by taking thederivative of this signal, integrating over a 100 ms moving window,zeroing the negative values, removing the large artifacts by zeroingvalues beyond 15× the median of the signal, zeroing the values below athreshold defined by the mean of the signal, and then searching forlocal maxima. Local maxima closer than a defined refractory period of300 ms to the preceding ones are dismissed. The result is a time seriesof pulse reference timings.

As is shown in 910, the foot IPG is low-pass filtered at 25 Hz with an8-pole Butterworth filter and inverted (so that pulses have an upwardpeak). Segments starting from the timings extracted (915) from the LegIPG (reference timings) and extending to 80% of the previous pulseinterval, but no longer than one second, are defined in the Foot IPG.This defines the time windows where the Foot IPG is expected to occur,avoiding misdetection outside of these windows. In each segment, thederivative of the signal is computed, and the point of maximum positivederivative (maximum acceleration) is extracted. The foot of the IPGsignal is then computed using an intersecting tangent method, where thefiducial (920) is defined by the intersection between a first tangent tothe IPG at the point of maximum positive derivative and a second tangentto the minimum of the IPG on the left of the maximum positive derivativewithin the segment.

The time series resulting from this two-step extraction is then used inconjunction with another signal to facilitate additional processing. Inthe present disclosure, these timings are used as reference timings toimprove the SNR of BCG signals to subsequently extract intervals betweena timing of the BCG (typically the I-wave) and the Foot IPG for thepurpose of computing the PWV, as previously disclosed in U.S.2013/0310700 (Wiard). In certain embodiments, the timings of the Leg IPGare used as reference timings to improve the SNR of BCG signals, and thefoot IPG timings are used to extract intervals between timing fiducialsof the improved BCG (typically the I-wave) and the Foot IPG for thepurpose of computing the PTT and the (PWV).

In certain embodiments, the processing steps include an individual pulseSNR computation after individual timings have been extracted, either inLeg IPG or Foot IPG. Following the computation of the SNRs, pulses witha SNR below a threshold value are eliminated from the time series, inorder to prevent propagating noise in subsequent processing steps. Theindividual SNRs may be computed in a variety of methods known to aperson skilled in the art. For instance, an estimated pulse can becomputed by ensemble averaging segments of signal around the pulsereference timing. The noise associated with each pulse is defined as thedifference between the pulse and the estimated pulse. The SNR is thenthe ratio of the root-mean-square (RMS) value of the estimated pulseover the RMS value of the noise for that pulse.

In certain embodiments, the time interval between the Leg IPG pulses,(as detected by the above-mentioned methods), and the Foot IPG pulses,also detected by the above-mentioned methods, is extracted. The Leg IPGmeasuring a pulse occurring earlier in the legs is compared to the pulsefrom the Foot IPG, the interval between these two being related to thepropagation speed in the lower body, i.e., the peripheral vasculature.This provides complementary information to the interval extractedbetween the BCG and the Foot IPG, for instance, and can be used todecouple central versus peripheral vascular properties. It is alsocomplementary to information derived from timings between the BCG andthe Leg ICG.

In FIG. 10, the Leg IP and the Foot IPG are simultaneously measured(1000), the Leg IPG is low-pass filtered (1005), the foot IPG islow-pass filtered (1010), and segments starting from the timings areextracted (1015) from the Leg IPG (reference timings). The segments ofthe Foot IPG extracted based on the Leg IPG timings areensemble-averaged (1020) to produce a higher SNR Foot IPG pulse. Fromthis ensemble-averaged signal, the start of the pulse is extracted usingthe same intersecting tangent approach as described earlier. Thisapproach enables the extraction of accurate timings in the Foot IPG evenif the impedance signal is dominated by noise. These timings can then beused together with timings extracted from the BCG for the purpose ofcomputing the PTT and (PWV). Timings derived from ensemble-averagedwaveforms and individual waveforms can also be both extracted, for thepurpose of comparison, averaging and error-detection.

Specific timings that can be extracted from the IPG pulses (from eitherleg or foot) are related (but not limited) to the peak of the pulse, tothe minimum preceding the peak, or to the maximum second derivative(maximum rate of acceleration) preceding the point of maximumderivative. An IPG pulse and the extraction of a fiducial (1025) in theIPG can also be performed by several other signal processing methods,including (but not limited to) template matching, cross-correlation,wavelet-decomposition, or short window Fourier transform.

In certain embodiments, a dual-Foot IPG is measured, allowing thedetection of blood pressure pulses in both feet. Such information can beused for diagnostic of peripheral arterial diseases (PAD) by comparingthe relative PATs in both feet to look for asymmetries. It can also beused to increase the robustness of the measurement by allowing one footto have poor contact with electrodes (or no contact at all). SNRmeasurements can be used to assess the quality of the signal in eachfoot, and to select the best signal for downstream analysis. Timingsextracted from each foot can be compared and set to flag potentiallyinaccurate PWV measurements due to arterial peripheral disease, in theevent these timings are different by more than a defined threshold.Alternatively, timings from both feet can be pooled to increase theoverall SNR if their difference is below a defined threshold.

In certain embodiments, the disclosure is used to measure a PWV, wherethe IPG is augmented by the addition of BCG sensing into the weighingscale to determine characteristic fiducials between the BCG and Leg IPGtrigger, or the BCG and Foot IPG. The BCG sensors are comprisedtypically of the same strain gage set used to determine the bodyweightof the user. The load cells are typically wired into a bridgeconfiguration to create a sensitive resistance change with smalldisplacements due to the ejection of the blood into the aorta, where thecirculatory or cardiovascular force produce movements within the body onthe nominal order of 1-3 Newtons. BCG forces can be greater than or lessthan the nominal range in cases such as high or low cardiac output.

FIG. 11 shows an example configuration to obtain the PTT, using thefirst IPG as the triggering pulse for the Foot IPG and BCG, consistentwith various aspects of the present disclosure. The I-wave of the BCG1100 as illustrated normally depicts the headward force due to cardiacejection of blood into the ascending aorta which can be used as a timingfiducial indicative of the pressure pulse initiation of the user'sproximal aorta relative to the user's heart. The J-wave is alsoindicative of timings in the systole phase and also incorporatesinformation related to the strength of cardiac ejection and the ejectionduration. The K-Wave also provides systolic and vascular information ofthe user's aorta. The characteristic timings of these and other BCGwaves can be used as fiducials that can be related to fiducials of theIPG signals of the present disclosure.

FIG. 12 shows another example of a scale 1200 with interleaved footelectrodes 1205 to inject and sense current from one foot to anotherfoot, and within one foot, consistent with various aspects of thepresent disclosure. FIG. 13A-C3 shows various examples of a scale 1300with interleaved foot electrodes 1305 to inject and sense current fromone foot to another foot, and measure Foot IPG signals in both feet,consistent with various aspects of the present disclosure. FIGS. 14A-Dshows an example breakdown of a scale 1400 with interleaved footelectrodes 1405 to inject and sense current from one foot to anotherfoot, and within one foot, consistent with various aspects of thepresent disclosure.

FIG. 15 shows an example block diagram of circuit-based building blocks,consistent with various aspects of the present disclosure. The variouscircuit-based building blocks shown in FIG. 15 can be implemented inconnection with the various aspects discussed herein. In the exampleshown, the block diagram includes foot electrodes 1500 that can collectthe IPG signals. Further, the block diagram includes strain gauges 1505,and an LED/photosensor 1510. The foot electrodes 1500 is configured witha leg impedance measurement circuit 1515, a foot impedance measurementcircuit 1520, and an optional second foot impedance measurement circuit1525. The leg impedance measurement circuit 1515, the foot impedancemeasurement circuit 1520, and the optional second foot impedancemeasurement circuit 1525 report the measurements collected to aprocessor circuit 1545.

The processor circuit 1545 also collects data from a weight measurementcircuit 1530 and an optional balance measurement circuit 1535 that areconfigured with the strain gauges 1505. Further, an optionalphotoplethysmogram (PPG) measurement circuit 1540, which collects datafrom the LED/photosensor 1510, can also provide data to the processorcircuit 1545.

The processor circuit 1545 is powered via a power circuit 1550. Further,the processor circuit 1545 also collects user input data from a userinterface 1555 that can include a touch screen and/or buttons. The datacollected/measured by the processor circuit 1545 is shown to the uservia a display 1560. Additionally, the data collected/measured by theprocessor circuit 1545 can be stored in a memory circuit 1580. Further,the processor circuit 1545 can optionally control a haptic feedbackcircuit 1565, a speaker or buzzer 1570, a wired/wireless interface 1575,and an auxiliary sensor 1585.

FIG. 16 shows an example flow diagram, consistent with various aspectsof the present disclosure. As shown in block 1600, a PWV length isentered. As is shown in block 1605, a user's weight, balance, leg, andfoot impedance are measured (as is consistent with various aspects ofthe present disclosure). As is shown at block 1610, the integrity ofsignals is checked (e.g., signal to noise ratio). If the signalintegrity check is not met, the user's weight, balance, leg, and footimpedance are measured again (block 1605), if the signals integritycheck is met, the leg impedance pulse timings are extracted (as is shownat block 1615). As is shown at block 1620, foot impedance and pulsetimings are then extracted, and as is shown at block 1625, BCG timingsare extracted. As is shown at block 1630, a timings quality check isperformed. If the timings quality check is not validated, the user'sweight, balance, leg and foot impedance are again measured (block 1605).If the timings quality check is validated, the PWV is calculated (as isshown at block 1635). Finally, as is shown at block 1640, the PWV isthen displayed to the user.

FIG. 17 shows an example scale 1700 communicatively coupled to awireless device, consistent with various aspects of the presentdisclosure. As described herein, a display 1705 displays the variousaspects measured by the scale 1700. The scale can also wirelesslybroadcast the measurements to a wireless device 1710.

FIGS. 18A-C show example impedance as measured through different partsof the foot based on the foot position, consistent with various aspectsof the present disclosure. For instance, example impedance measurementconfigurations may be implemented using a dynamic electrodeconfiguration for measurement of foot impedance and related timings,consistent with various aspects of the present disclosure. Dynamicelectrode configuration may be implemented usingindependently-configurable electrodes to optimize the impedancemeasurement. As shown in FIG. 18A, interleaved electrodes 1800 areconnected to an impedance processor circuit 1805 to determine footlength, foot position, and/or foot impedance. As is shown in FIG. 18B,an impedance measurement is determined regardless of foot position 1810based on measurement of the placement of the foot across the electrodes1800. This is based in part in the electrodes 1800 that are engaged(blackened) and in contact with the foot (based on the foot position1810), which is shown in FIG. 18C.

More specifically regarding FIG. 18A, configuration can includeconnection/de-connection of the individual electrodes 1800 to theimpedance processor circuit 1805, their configuration ascurrent-carrying electrodes (injection or return), sense electrodes(positive or negative), or both. The configuration can either be presetbased on user information, or updated at each measurement (dynamicreconfiguration) to optimize a given parameter (impedance SNR,measurement location). The system may for instance algorithmicallydetermine which electrodes under the foot to use in order to obtain thehighest SNR in the pulse impedance signal. Such optimization algorithmmay include iteratively switching configurations and measuring theresulting impedance, then selecting the best-suited configuration.Alternatively, the system may first, through a sequential impedancemeasurement between each individual electrode 1800 and another electrodein contact with the body (such as an electrode in electrode pair 205 onthe other foot), determine which electrodes are in contact with thefoot. By determining the two most apart electrodes, the foot size isdetermined. Heel location can also be determined in this manner, as canother characteristics such as foot arch type. These parameters can thenbe used to determine programmatically (in an automated manner byCPU/logic circuitry) which electrodes should be selected for currentinjection and return (as well as sensing if a Kelvin connection issued)in order to obtain the best foot IPG.

In various embodiments involving the dynamically reconfigurableelectrode array 1800/1805, an electrode array set is selected to measurethe same portion (or segment) of the foot, irrespective of the footlocation on the array. FIG. 18B illustrates the case of several footpositions on a static array (a fixed set of electrodes are used formeasurement at the heel and plantar/toe areas, with a fixed gap of aninactive electrode or insulating material between them). Depending onthe position of the foot, the active electrodes are contacting the footat different locations, thereby sensing a different volume (or segment)of the foot. If the IPG is used by itself (e.g., for heart measurement),such discrepancies may be non-consequential. However, if timings derivedfrom the IPG are referred to other timings (e.g., R-wave from the ECG,or specific timing in the BCG), such as for the calculation of a PTT orPWV, the small shifts in IPG timings due to the sensing of slightlydifferent volumes in the foot (e.g., if the foot is not always placed atthe same position on the electrodes) can introduce an error in thecalculation of the interval. Such location variations can readily occurin the day-to-day use of the scale. With respect to FIG. 18B forinstance, the timing of the peak of the IPG from the foot placement onthe right (sensing the toe/plantar region) would be later than from thefoot placement on the left, which senses more of the heel volume (thepulse reaches first the heel, then the plantar region). Factorsinfluencing the magnitude of these discrepancies include foot shape(flat or not) and foot length.

Various embodiments address challenges relating to foot placement. FIG.18C shows an example embodiment involving dynamic reconfiguration of theelectrodes to reduce such foot placement-induced variations. As anexample, by sensing the location of the heel first (as described above),it is possible to activate only a subset of electrodes under the heel,and another subset of electrodes separated by a fixed distance (1800).The other electrodes (e.g., unused electrodes) are left disconnected.The sensed volume will therefore always be the same, producingconsistent timings. The electrode configuration leading to the mostconsistent results may also be informed by the foot impedance, footlength, the type of arch (all of which can be measured by the electrodearray as shown above), but also by the user ID (foot information can bestored for each user, then looked up based on automatic user recognitionor manual selection (e.g., in a look-up-table stored for each user in amemory circuit accessible by the CPU circuit in the scale)).

Accordingly, in certain embodiments, the impedance-measurement apparatusmeasures impedance using a plurality of electrodes contacting one footand with at least one other electrode (typically many) at a locationdistal from the foot. The plurality of electrodes (contacting the onefoot) is arranged on the platform and in a pattern configured to injectcurrent signals and sense signals in response thereto, for the samesegment of the foot so that the timing of the pulse-based measurementsdoes not vary simply because the user placed the one foot at a slightlydifferent position on the platform or scale. Thus, in FIG. 18A, thefoot-to-electrode locations for the heel are different locations thanthat shown in FIGS. 18B and 18C. As this different foot placement mightoccur from day to day for the user, the timing and related impedancemeasurements should be for the same (internal) segment of the foot. Byhaving the computer processor circuit inject current and senseresponsive signals to first locate the foot on the electrodes (e.g.,sensing where positions of the foot's heel plantar regions and/or toes),the pattern of foot-to-electrode locations permits the foot to movelaterally, horizontally and both laterally and horizontally via thedifferent electrode locations, while collecting impedance measurementsrelative to the same segment of the foot.

The BCG/IPG system can be used to determine the PTT of the user, byidentification of the average I-Wave or derivative timing near theI-Wave from a plurality of BCG heartbeat signals obtained simultaneouslywith the Dual-IPG measurements of the present disclosure to determinethe relative PTT along an arterial segment between the ascending aorticarch and distal pulse timing of the user's lower extremity. In certainembodiments, the BCG/IPG system is used to determine the PWV of theuser, by identification of the characteristic length representing thelength of the user's arteries, and by identification of the averageI-Wave or derivative timing near the I-Wave from a plurality of BCGheartbeat signals obtained simultaneously with the Dual-IPG measurementsof the present disclosure to determine the relative PTT along anarterial segment between the ascending aortic arch and distal pulsetiming of the user's lower extremity. The system of the presentdisclosure and alternate embodiments may be suitable for determining thearterial stiffness (or arterial compliance) and/or cardiovascular riskof the user regardless of the position of the user's feet within thebounds of the interleaved electrodes. In certain embodiments, theweighing scale system incorporates the use of strain gage load cells andsix or eight electrodes to measure a plurality of signals including:bodyweight, BCG, body mass index, fat percentage, muscle masspercentage, and body water percentage, heart rate, heart ratevariability, PTT, and PWV measured simultaneously or synchronously whenthe user stands on the scale to provide a comprehensive analysis of thehealth and wellness of the user.

In other certain embodiments, the PTT and PWV are computed using timingsfrom the Leg IPG or Foot IPG for arrival times, and using timings from asensor located on the upper body (as opposed to the scale measuring theBCG) to detect the start of the pulse. Such sensor may include animpedance sensor for impedance cardiography, a hand-to-hand impedancesensor, a photoplethysmogram on the chest, neck, head, arms or hands, oran accelerometer on the chest (seismocardiograph) or head.

Communication of the biometric information is another aspect of thepresent disclosure. The biometric results from the user are then storedin the memory on the scale and displayed to the user via a display onthe scale, audible communication from the scale, and/or the data iscommunicated to a peripheral device such as a computer, smart phone, ortablet computing device. The communication occurs directly to theperipheral device with a wired connection, or can be sent to theperipheral device through wireless communication protocols such asBluetooth or WiFi. Computations such as signal analyses describedtherein may be carried out locally on the scale, in a smartphone orcomputer, or in a remote processor (cloud computing).

Other aspects of the present disclosure are directed toward apparatusesor methods that include the use of at least two electrodes that contactfeet of a user. Further, circuitry is provided to determine a pulsearrival time at the foot based on the recording of two or more impedancesignals from the set of electrodes. Additionally, a second set ofcircuitry is provided to extract a first pulse arrival time from a firstimpedance signal and use the first pulse arrival time as a timingreference to extract and process a second pulse arrival time in a secondimpedance signal.

Reference may also be made to the following published patent documents,U.S. Patent Publication 2010/0094147 and U.S. Patent Publication2013/0310700, which are, together with the references cited therein,herein fully incorporated by reference for the purposes of sensors andsensing technology. The aspects discussed therein may be implemented inconnection with one or more of embodiments and implementations of thepresent disclosure (as well as with those shown in the figures). In viewof the description herein, those skilled in the art will recognize thatmany changes may be made thereto without departing from the spirit andscope of the present disclosure.

As illustrated herein, various circuit-based building blocks and/ormodules may be implemented to carry out one or more of the operationsand activities described herein shown in the block-diagram-type figures.In such contexts, these building blocks and/or modules representcircuits that carry out one or more of these or relatedoperations/activities. For example, in certain of the embodimentsdiscussed above (such as the pulse circuitry modularized as shown inFIGS. 8A-B), one or more blocks/modules are discrete logic circuits orprogrammable logic circuits configured and arranged for implementingthese operations/activities, as in the circuit blocks/modules shown. Incertain embodiments, the programmable circuit is one or more computercircuits programmed to execute a set (or sets) of instructions (and/orconfiguration data). The instructions (and/or configuration data) can bein the form of firmware or software stored in and accessible form, amemory (circuit). As an example, first and second modules/blocks includea combination of a CPU hardware-based circuit and a set of instructionsin the form of firmware, where the first module/block includes a firstCPU hardware circuit with one set of instructions and the secondmodule/block includes a second CPU hardware circuit with another set ofinstructions.

Based upon the above discussion and illustrations, those skilled in theart will readily recognize that various modifications and changes may bemade to the present disclosure without strictly following the exemplaryembodiments and applications illustrated and described herein. Forexample, the input terminals as shown and discussed may be replaced withterminals of different arrangements, and different types and numbers ofinput configurations (e.g., involving different types of input circuitsand related connectivity). Such modifications do not depart from thetrue spirit and scope of the present disclosure, including that setforth in the following claims.

What is claimed is:
 1. A weighing scale comprising: a platform regionconfigured and arranged to support a user while the user stands on theplatform region; and a base unit configured and arranged to integrate asupport structure including the platform region and sensor circuitrytherein, the platform region configured and arranged to engage the userwith the sensor circuitry while the user stands on the platform region,and to collect physiological data from the user via the sensorcircuitry, a display configured and arranged with the support structurefor displaying data through the platform region, user-targeted circuitrylocated in the base unit and configured and arranged to operate in afitness testing mode by instructing a user to engage the sensorcircuitry via the platform region, during a reduced-exertion state ofthe user, the sensor circuitry being responsive to the engaging bycollecting physiological data from the user, the physiological databeing indicative of baseline values, to change the user's heart rate byincreasing or decreasing physical exertion, and to engage the sensorcircuitry via the platform region, after instructing the user to changethe user's heart rate, the sensor circuitry being responsive to theengaging by collecting physiological data from the user indicative of aphysical exertion state of the user relative to the baseline values,receive the physiological data from the sensor circuitry, determinephysiological parameters of the user based on respective sets of thephysiological data and a physical exertion state associated with eachset; and a communication driver configured and arranged to provideinformation, based on the determined physiological parameters, from theuser-targeted circuitry to the display for viewing by the user throughthe platform region and to recognize whether the user is standing on theplatform region and, in response thereto, present information via alarge-area display mode when the user is not standing on the platformregion and, via a reduced-area display mode in a reduced-area displayregion of the platform region which is adjacent to feet of the user,when the user is standing on the platform region, present informationthat corresponds to the physiological parameters of the user.
 2. Theweighing scale of claim 1, wherein the user-targeted circuitry isconfigured and arranged to: instruct the user to change the user's heartrate by increasing physical exertion, immediately prior to the userengaging the sensor circuitry and collecting the physiological dataindicative of the physical exertion state of the user, after collectingthe physiological data indicative of baseline values, instruct the userto change the user's heart rate by reducing exertion and thereafter tore-engage the sensor circuitry via the platform region, thereincollecting physiological data indicative of the reduced-exertion state,and determine the physiological parameters of the user based on thephysiological data collected after the user has reduced exertion,relative to the physiological data indicative of the physical exertionstate of the user.
 3. The weighing scale of claim 1, wherein theuser-targeted circuitry is further configured and arranged to correlatethe physiological parameters in each of a plurality of physical exertionstates to determine the physical health of the user.
 4. The weighingscale of claim 1, wherein the user-targeted circuitry is furtherconfigured and arranged to determine, in response to determining thephysical fitness of the user, actions to encourage improvement of theuser's physical fitness and to display information pertaining to theactions via the display.
 5. The weighing scale of claim 1, wherein thedisplay is further configured and arranged to receive touch signal dataindicative of engagement of the user on the platform region and anassociated position and movement of the user, and the communicationdriver is further configured and arranged to receive the touch signaldata from the display, process the touch signals, and determine theassociated position and movement with such touch signals.
 6. Theweighing scale of claim 1, wherein the user-targeted circuitry isfurther configured and arranged to receive externally acquiredphysiological data from external personal electronic devices, and usethe externally acquired data, in conjunction with the physiological dataacquired from the sensor circuitry, to determine the physiologicalparameters of the user.
 7. The weighing scale of claim 1, wherein theplatform region and the sensor circuitry are further configured andarranged with electrodes that are configured and arranged to engage atleast one foot of the user while the user stands on the platform region.8. The weighing scale of claim 1, wherein the platform region and thesensor circuitry are further configured and arranged with interleavedelectrodes that are configured and arranged to inject and sense current,while the user stands on the platform region, from one foot of the userto another foot of the user, and within one foot of the user.
 9. Theweighing scale of claim 1, wherein the platform region and the sensorcircuitry are further configured and arranged with a set of electrodesthat are configured and arranged to engage feet of the user while theuser stands on the platform region, and wherein the user-targetedcircuitry includes a processor configured and arranged to select asubset of the set of electrodes for a biometric measurement based on alocation of the user's feet relative to the set of electrodes while theuser stands on the platform region.
 10. A weighing scale comprising: aplatform region configured and arranged to support a user while the userstands on the platform region; and a base unit configured and arrangedto integrate a support structure including the platform region andsensor circuitry therein, the platform region configured and arranged toengage the user with the sensor circuitry while the user stands on theplatform region, and to collect physiological data from the user via thesensor circuitry, a display configured and arranged with the supportstructure for displaying data through the platform region, user-targetedcircuitry located in the base unit and configured and arranged tooperate in a fitness testing mode by instructing a user to engage thesensor circuitry via the platform region, during a reduced-exertionstate of the user, the sensor circuitry being responsive to the engagingby collecting physiological data from the user, the physiological databeing indicative of baseline values, to change the user's heart rate byincreasing or decreasing physical exertion, and to engage the sensorcircuitry via the platform region, after instructing the user to changethe user's heart rate, the sensor circuitry being responsive to theengaging by collecting physiological data from the user indicative of aphysical exertion state of the user relative to the baseline values,receive the physiological data from the sensor circuitry, determinephysiological parameters of the user based on respective sets of thephysiological data and a physical exertion state associated with eachset; a communication driver configured and arranged to provideinformation, based on the determined physiological parameters, from theuser-targeted circuitry to the display for viewing by the user throughthe platform region; a camera configured and arranged to capture imagedata indicative of an area around the base unit and presence of theuser; image processing circuitry configured and arranged to receive thecaptured image data from the camera and determine color and patternthemes associated with the image data of the area around the base unit,and the presence of the user; and the display is further configured andarranged in an active mode, determined by presence of the user by theimage processing circuitry, to present information that corresponds tothe physiological parameters of the user, in an idle mode, determined bynon-presence of the user by the image processing circuitry, to presentan image indicative of the area around the base unit, based on the imagedata processed by the image processing circuitry.
 11. A weighing scalecomprising: a platform region configured and arranged to support a userwhile the user stands on the platform region; and a base unit configuredand arranged to integrate a support structure including the platformregion and sensor circuitry therein, the platform region configured andarranged to engage the user with the sensor circuitry while the userstands on the platform region, and to collect physiological data fromthe user via the sensor circuitry, a display configured and arrangedwith the support structure for displaying data through the platformregion, user-targeted circuitry located in the base unit and configuredand arranged to operate in a fitness testing mode by instructing a userto engage the sensor circuitry via the platform region, during areduced-exertion state of the user, the sensor circuitry beingresponsive to the engaging by collecting physiological data from theuser, the physiological data being indicative of baseline values, tochange the user's heart rate by increasing or decreasing physicalexertion, and to engage the sensor circuitry via the platform region,after instructing the user to change the user's heart rate, the sensorcircuitry being responsive to the engaging by collecting physiologicaldata from the user indicative of a physical exertion state of the userrelative to the baseline values, receive the physiological data from thesensor circuitry, determine physiological parameters of the user basedon respective sets of the physiological data and a physical exertionstate associated with each set; and a communication driver configuredand arranged to provide information, based on the determinedphysiological parameters, from the user-targeted circuitry to thedisplay for viewing by the user through the platform region and torecognize whether the user is standing on the platform region and, inresponse thereto, present information via a large-area display mode whenthe user is not standing on the platform region and, via a reduced-areadisplay mode in a reduced-area display region of the platform regionwhich is adjacent to feet of the user, when the user is standing on theplatform region, present information that corresponds to thephysiological parameters of the user, wherein the user-targetedcircuitry is further configured and arranged to receive externallyacquired physiological data from at least one external personalelectronic device including a computer, and to use the externallyacquired data, in conjunction with the physiological data acquired fromthe sensor circuitry for assessing a physiological condition of theuser.